Apparatuses and methods for determining tear film break-up time and/or for detecting lid margin contact and blink rates, particulary for diagnosing, measuring, and/or analyzing dry eye  conditions and symptoms

ABSTRACT

Embodiments disclosed herein include devices, systems, and methods for determining tear film break-up time and for detecting eyelid margin contact and blink rates, particularly for diagnosing, measuring, and/or analyzing dry eye conditions and symptoms. The apparatus and methods for determining tear film break-up time and for detecting eyelid margin contact and blink rates, particularly for diagnosing, measuring, and/or analyzing dry eye conditions and symptoms may employ ocular surface interferometry (OSI) devices or other imaging and display devices capable of imaging and displaying a picture of a patient&#39;s eye during tear film break-up time and blink rate related procedures.

PRIORITY APPLICATION

The present application claims priority to U.S. Provisional Patent Application No. 61/642,719 entitled “APPARATUSES AND METHODS FOR DETERMINING TEAR FILM BREAK-UP TIME AND/OR FOR DETECTING LID MARGIN CONTACT AND BLINK RATES, PARTICULARLY FOR DIAGNOSING, MEASURING, AND/OR ANALYZING DRY EYE CONDITIONS AND SYMPTOMS,” filed May 4, 2012, which is incorporated herein by reference in its entirety.

RELATED APPLICATIONS

The present application is related to U.S. patent application Ser. No. 13/870,054 entitled “APPARATUSES AND METHODS OF OCULAR SURFACE INTERFEROMETRY (OSI) EMPLOYING POLARIZATION AND SUBTRACTION FOR IMAGING, PROCESSING, AND/OR DISPLAYING AN OCULAR TEAR FILM,” filed Apr. 25, 2013, which claims priority to U.S. Provisional Patent Application No. 61/638,231 entitled “APPARATUSES AND METHODS OF OCULAR SURFACE INTERFEROMETRY (OSI) EMPLOYING POLARIZATION AND SUBTRACTION FOR IMAGING, PROCESSING, AND/OR DISPLAYING AN OCULAR TEAR FILM,” filed Apr. 25, 2012, which are both incorporated herein by reference in their entireties.

The present application is also related to U.S. patent application Ser. No. 13/870,214 entitled “BACKGROUND REDUCTION APPARATUSES AND METHODS OF OCULAR SURFACE INTERFEROMETRY (OSI) EMPLOYING POLARIZATION FOR IMAGING, PROCESSING, AND/OR DISPLAYING AN OCULAR TEAR FILM,” filed Apr. 25, 2013, which claims priority to U.S. Provisional Patent Application No. 61/638,260 entitled “BACKGROUND REDUCTION APPARATUSES AND METHODS OF OCULAR SURFACE INTERFEROMETRY (OSI) EMPLOYING POLARIZATION FOR IMAGING, PROCESSING, AND/OR DISPLAYING AN OCULAR TEAR FILM”, filed on Apr. 25, 2012, which are both incorporated herein by reference in their entireties.

The present application is also related to U.S. patent application Ser. No. 12/798,325 entitled “OCULAR SURFACE INTERFEROMETRY (OSI) METHODS FOR IMAGING, PROCESSING, AND/OR DISPLAYING AN OCULAR TEAR FILM,” filed Apr. 1, 2010, which claims priority to U.S. Provisional Patent Application No. 61/211,596 entitled “OCULAR SURFACE INTERFEROMETRY (OSI) DEVICES, SYSTEMS, AND METHODS FOR MEASURING TEAR FILM LAYER THICKNESS(ES),” filed on Apr. 1, 2009, which are both incorporated herein by reference in their entireties.

The present application is also related to U.S. patent application Ser. No. 12/798,275 entitled “OCULAR SURFACE INTERFEROMETRY (OSI) DEVICES AND SYSTEMS FOR IMAGING, PROCESSING, AND/OR DISPLAYING AN OCULAR TEAR FILM,” filed on Apr. 1, 2010, which is incorporated herein by reference in its entirety.

The present application is also related to U.S. patent application Ser. No. 12/798,326 entitled “OCULAR SURFACE INTERFEROMETRY (OSI) METHODS FOR IMAGING AND MEASURING OCULAR TEAR FILM LAYER THICKNESS(ES),” filed on Apr. 1, 2010, issued as U.S. Pat. No. 8,092,023, which is incorporated herein by reference in its entirety.

The present application is also related to U.S. patent application Ser. No. 12/798,324 entitled “OCULAR SURFACE INTERFEROMETRY (OSI) DEVICES AND SYSTEMS FOR IMAGING AND MEASURING OCULAR TEAR FILM LAYER THICKNESS(ES),” filed on Apr. 1, 2010, issued as U.S. Pat. No. 8,215,774, which is incorporated herein by reference in its entirety.

The present application is also related to U.S. patent application Ser. No. 11/820,664 entitled “TEAR FILM MEASUREMENT,” filed on Jun. 20, 2007, issued as U.S. Pat. No. 7,758,190, which is incorporated herein by reference in its entirety.

The present application is also related to U.S. patent application Ser. No. 11/900,314 entitled “TEAR FILM MEASUREMENT,” filed on Sep. 11, 2007, issued as U.S. Pat. No. 8,192,026, which is incorporated herein by reference in its entirety.

The present application is being filed with three (3) sets of color versions of the drawings discussed and referenced in this disclosure. Color drawings more fully disclose the subject matter disclosed herein.

FIELD OF THE DISCLOSURE

The technology of the disclosure relates to determining ocular tear film break-up time as a method to determine and diagnose dry-eye conditions due to aqueous layer and/or lipid layer deficiencies, including but not limited to evaporative dry-eye and/or meibomian gland dysfunction (MGD). The technology of the disclosure also relates to detecting eyelid margin contact, whether complete or partial eyelid margin contact, and blink rates as it may relate to dry-eye conditions.

BACKGROUND

In the human eye, the precorneal tear film covering ocular surfaces is composed of three primary layers: the mucin layer, the aqueous layer, and the lipid layer. Each layer plays a role in the protection and lubrication of the eye and thus affects dryness of the eye or lack thereof. Dryness of the eye is a recognized ocular disease, which is generally referred to as “dry eye,” “dry eye syndrome” (DES), or “keratoconjunctivitis sicca” (KCS). Dry eye can cause symptoms, such as itchiness, burning, and irritation, which can result in discomfort. There is a correlation between the ocular tear film layer thicknesses and dry eye disease. The various different medical conditions and damage to the eye as well as the relationship of the aqueous and lipid layers to those conditions are reviewed in Sury Opthalmol 52:369-374, 2007 and additionally briefly discussed below.

As illustrated in FIG. 1, the precorneal tear film includes an innermost layer of the tear film in contact with a cornea 10 of an eye 11 known as the mucus layer 12. The mucus layer 12 is comprised of many mucins. The mucins serve to retain aqueous in the middle layer of the tear film known as the aqueous layer. Thus, the mucus layer 12 is important in that it assists in the retention of aqueous on the cornea 10 to provide a protective layer and lubrication, which prevents dryness of the eye 11.

A middle or aqueous layer 14 comprises the bulk of the tear film. The aqueous layer 14 is formed by secretion of aqueous by lacrimal glands 16 and accessory tear glands 17 surrounding the eye 11, as illustrated in FIG. 2. The aqueous, secreted by the lacrimal glands 16 and accessory tear glands 17, is also commonly referred to as “tears.” One function of the aqueous layer 14 is to help flush out any dust, debris, or foreign objects that may get into the eye 11. Another important function of the aqueous layer 14 is to provide a protective layer and lubrication to the eye 11 to keep it moist and comfortable. Defects that cause a lack of sufficient aqueous in the aqueous layer 14, also known as “aqueous deficiency,” are a common cause of dry eye. Contact lens wear can also contribute to dry eye. A contact lens can disrupt the natural tear film and can reduce corneal sensitivity over time, which can cause a reduction in tear production.

The outermost layer of the tear film, known as the “lipid layer” 18 and also illustrated in FIG. 1, also aids to prevent dryness of the eye. The lipid layer 18 is comprised of many lipids known as “meibum” or “sebum” that is produced by meibomian glands 20 in upper and lower eyelids 22, 24, as illustrated in FIG. 3. This outermost lipid layer is very thin, typically less than 250 nanometers (nm) in thickness. The lipid layer 18 provides a protective coating over the aqueous layer 14 to limit the rate at which the aqueous layer 14 evaporates. Blinking causes the upper eyelid 22 to mall up aqueous and lipids as a tear film, thus forming a protective coating over the eye 11. A higher rate of evaporation of the aqueous layer 14 can cause dryness of the eye. Thus, if the lipid layer 18 is not sufficient to limit the rate of evaporation of the aqueous layer 14, dryness of the eye may result.

Notwithstanding the foregoing, it has been a long standing and vexing problem for clinicians and scientists to quantify the lipid and aqueous layers and any deficiencies of same to diagnose evaporative tear loss and/or tear deficiency dry eye conditions. Further, many promising treatments for dry eye have failed to receive approval from the United States Food and Drug Administration due to the inability to demonstrate clinical effectiveness to the satisfaction of the agency. Many clinicians diagnose dry eye based on patient symptoms alone. Questionnaires have been used in this regard. Although it seems reasonable to diagnose dry eye based on symptoms alone, symptoms of ocular discomfort represent only one aspect of “dry eyes,” as defined by the National Eye Institute workshop on dry eyes. In the absence of a demonstrable diagnosis of tear deficiency or a possibility of excessive tear evaporation and damage to the exposed surface of the eye, one cannot really satisfy the requirements of dry eye diagnosis.

In addition, the importance of the lipid layer on dry eye syndrome has been well studied (See FIG. 1 for the lipid layer on the cornea of the eye). The creation of normal tear film is a continuous process and the etiology has been well described. With adequate meibomian gland function and proper blinking, proper tear film is maintained. One method of visualizing the duration of tear film is to ask a patient to keep their eyes open and visualizing the tear film through the use of fluorescein strips or other devices. In patients with dry eyes, the tear film is less stable, and breaks up faster and results in a quicker break-up time. Longer durations before tear film break-up indicates healthier tear film and meibomian gland function.

One known method for determining tear break-up time is Fluorescein Break-up Time (FBUT). FBUT is performed with a strip of fluorescein that is applied in the lower eyelid fornix and then quickly removed. The patient will be asked to blink three times and then look into the slit lamp without trying to blink. Using a cobalt-blue filtered light and a slitlamp microscope, a measurement is taken of the amount of time that elapses from the last blink and appearance of the first break in the tear film (a break will be seen by the appearance of a dark spot in the blue field). Typically in clinical practice this is done with a stop watch. FBUT of less than 10 seconds or less is consistent with dry eyes.

However, there are problems with FBUT. For example, the physical application of the fluorescein filter paper strip to the conjunctiva can stimulate tearing. In addition, the mere presence of fluorescein may change the properties of the tear film. Other methods have been tried to avoid using fluoresecein, such as using a keratometer, a keratoscope, or a Tearscope. These methods are termed Non Invasive Break-up Time, or NIBUT. Another technique is to analyze the prerupture phase of the tear film break-up referred to as Tear Thinning Time, or TTT, in which the distortion that occurs on the image of the eye is viewed. However, in all of these methods, the improper use of a stop watch or imperfect methods of detecting tear break up or the prerupture phase of the tear film can result in error. None of these methods provide a quantitative method of determining an amount of time for an area of interest to change on a surface of an eye.

Further, dry eye sufferers are affected in their abilities to perform everyday activities due to the persistent irritation and eye strain that can occur as a result of long periods of computer terminal use. Deficiency in their lipid layer thickness of the eye can be exasperated by partial or incomplete blinking. For example, the number of complete blinks would increase the higher the position of gaze of the individual. So if an individual were looking at a computer which was ten (10) degrees above eye level, they would need more complete blinks than if the computer were at eye level. Similarly if the computer monitor were placed below eye level significantly, there would be the need for fewer blinks because the rate of evaporation from the eye would decrease as the height of the exposed aperture decreases. These factors have been studied and published as work place safety and ergonomic studies have indicated the effect eye strain on productivity and worker satisfaction. Besides eye level position, other qualifiers are a factor, such as the context of the work, local humidity, type of task, age, skin color etc. of any one individual.

Thus, there is also a need to be able to observe blinking in a standardized method to determine whether or not the lids touched during the blinking process. The importance of the lipid layer on dry eye syndrome has been well studied (See FIG. 1 for the lipid layer on the cornea of the eye). The blink of the upper eyelid can maintain a sufficient lipid layer and the normal blink, defined by complete closure of the upper eyelid to the lower eyelid may not always occur.

For the purposes of this discussion, there are two types of blinks; the complete blink in which the upper eyelid makes contact on the lower eyelid throughout the margin of the eyelid, and the partial blink in which a portion or all of the eyelid margin is not in contact with each other. There needs to be a significant percentage of blinks to be complete to maintain the normal lipid layer of the eye. It would be clinically useful to be able to observe blinking in a standardized method to determine whether or not the lids touched during the blinking process. It is only when lids are shut completely, and then reopened, that oil is released from the meibomian glands. The exact ratio of how many blinks should be complete versus those that are partial blinks (i.e. where the lids do not touch) has never been determined. The study of blink rate is voluminous but there has not been a quantifiable study on the amplitude of the blink, types of blinks (complete versus partial) during a specific time periods, or the percentage of blinks that adequately resurface the cornea with lipids. Determining the amount of travel of the blink will indicate what is normal and not normal for these patients. With this information, the clinician can better inform patients in regards to their symptoms or condition, provide eyelid exercises, or propose additional therapy to alleviate the symptoms of dry eye. Currently, there is no standardized quantitative method for analyzing partial blinking.

SUMMARY OF THE DETAILED DESCRIPTION

Embodiments of the detailed description include devices, systems, and methods for determining tear film break-up time and for detecting eyelid margin contact and blink rates, particularly for diagnosing, measuring, and/or analyzing dry eye conditions and symptoms. The apparatus and methods for determining tear film break-up time and for detecting eyelid margin contact and blink rates, particularly for diagnosing, measuring, and/or analyzing dry eye conditions and symptoms may employ ocular surface interferometry (OSI) devices or other imaging and display devices capable of imaging and displaying a picture of a patient's eye during tear film break-up time and blink rate related procedures.

In this regard, in one embodiment, an apparatus for determining a break-up time of an ocular tear film is provided. The apparatus includes a control system. The control system is a control system configured to receive at least one first image of an area of interest of an ocular tear film captured by an imaging device while illuminated by a light source. The control system is also configured to start a time measurement instrument. The control system is also configured to receive at least one second image of the area of interest of the ocular tear film captured by the imaging device while illuminated by the light source. The control system is also configured to analyze the at least one first image and the at least one second image to determine if a change has occurred in the area of interest. The control system is also configured to determine if a threshold level has been reached if a change has occurred in the area of interest. The control system is also configured to measure an amount of time from the start of the time measurement instrument until a time that the threshold level has been reached if the threshold level has been reached.

In another embodiment, an apparatus for determining a break-up time of an ocular tear film is provided. The apparatus includes a control system. The control system is configured to receive at least one first image of an area of interest of an ocular tear film captured by an imaging device while illuminated by a light source of a first type, wherein the area of interest is divided into a plurality of segments and the at least one first image is of a first segment of the plurality of segments. In one embodiment, the light of the first type may be a polarized light source. The control system is further configured to start a time measurement instrument. The control system is also configured to receive at least one second image of an area of interest of an ocular tear film captured by an imaging device while illuminated by a light source of the first type, wherein the area of interest is divided into a plurality of segments and the at least one second image is of the first segment of the plurality of segments. The control system is configured to analyze the at least one first image and the at least one second image to determine if a change has occurred in the area of interest. The control system is also configured to receive at least one third image of an area of interest of the ocular tear film captured by the imaging device while illuminated by a light source of a second type, wherein the area of interest is divided into a plurality of segments and the at least one third image is of a second segment of the plurality of segments. In one embodiment, the light source of the second type may be a light source with a cobalt blue filter. The control system is also configured to receive at least one fourth image of an area of interest of the ocular tear film captured by the imaging device while illuminated by a light source of a second type, wherein the area of interest is divided into a plurality of segments and the at least one fourth image is of the second segment of the plurality of segments. The control system is further configured to analyze the at least one third image and the at least one fourth image to determine if a change has occurred in the area of interest. If a change has occurred in the area of interest based on any of the first image, second image, third image, and fourth image, the control system is configured to determine if a threshold level has been reached. If the threshold level has been reached, the control system is configured to measure an amount of time from the start of the time measurement instrument until a time that the threshold level has been reached.

In another embodiment, a method for determining a break-up time of an ocular tear film is provided. The method comprises receiving at least one first image of an area of interest of an ocular tear film captured by an imaging device while illuminated by a light source. The method also comprises starting a time measurement instrument. Then at least one second image of the area of interest of the ocular tear film captured by the imaging device while illuminated by the light source is received. The method also comprises analyzing the at least one first image and the at least one second image to determine if a change has occurred in the area of interest. If a change has occurred in the area of interest, the method further comprises determining if a threshold level has been reached. If the threshold level has been reached, the method also comprises measuring an amount of time from the start of the time measurement instrument until a time that the threshold level has been reached.

In another embodiment, a method for determining a break-up time of an ocular tear film is disclosed. The method includes receiving at least one first image of an area of interest of an ocular tear film captured by an imaging device while illuminated by a light source of a first type, wherein the area of interest is divided into a plurality of segments and the at least one first image is of a first segment of the plurality of segments. The method also comprises starting a time measurement instrument. The method further comprises receiving at least one second image of an area of interest of an ocular tear film captured by an imaging device while illuminated by a light source of the first type, wherein the area of interest is divided into a plurality of segments and the at least one second image is of the first segment of the plurality of segments. The at least one first image and the at least one second image are then analyzed to determine if a change has occurred in the area of interest. The method also comprises receiving at least one third image of an area of interest of the ocular tear film captured by the imaging device while illuminated by a light source of a second type, wherein the area of interest is divided into a plurality of segments and the at least one third image is of a second segment of the plurality of segments, and receiving at least one fourth image of an area of interest of the ocular tear film captured by the imaging device while illuminated by a light source of a second type, wherein the area of interest is divided into a plurality of segments and the at least one fourth image is of the second segment of the plurality of segments. The at least one third image and the at least one fourth image are analyzed to determine if a change has occurred in the area of interest. If a change has occurred in the area of interest based on any of the first image, second image, third image, and fourth images, the method also comprises determining if a threshold level has been reached. If the threshold level has been reached, the method further comprises measuring an amount of time from the start of the time measurement instrument until a time that the threshold level has been reached.

In another embodiment, an apparatus for determining lid margin contact and/or blink rate of an eye having an upper eyelid and a lower eyelid is provided. The control system is configured to receive at least one image of an area of interest of an eye captured by an imaging device when illuminated by a light source, wherein the at least one image is captured by the imaging device over a given period of time. The control system is also configured to analyze the at least one image to determine a number of complete blinks of the eye for the given period of time. In one non-limiting embodiment, the control system is further configured to analyze the at least one image to determine a number of partial blinks of the eye for the given period of time.

In another embodiment, a method for determining lid margin contact and/or blink rate of an eye having an upper eyelid and a lower eyelid is disclosed. The method comprises receiving at least one image of an area of interest of an eye captured by an imaging device when illuminated by a light source, wherein the at least one image is captured by the imaging device over a given period of time. The method also comprises analyzing the at least one image to determine a number of complete blinks of the eye for the given period of time. In one embodiment, the method also comprises analyzing the at least one image to determine a number of partial blinks of the eye for the given period of time.

To determine and measure tear film break-up times and analyze eyelid contract and blink rates of an eye, ocular surface interferometry (OSI) devices may be employed. Thus, other embodiments of the detailed description include and describe exemplary OSI devices, systems, and methods for imaging an ocular tear film and/or measuring a tear film layer thickness (TFLT) of a mammalian's ocular tear film. The OSI devices, systems, and methods can be used to measure the thickness of the lipid layer component (LLT) and/or the aqueous layer component (ALT) of the ocular tear film. “TFLT” as used herein includes LLT, ALT, or both LLT and ALT. “Measuring TFLT” as used herein includes measuring LLT, ALT, or both LLT and ALT. Imaging the ocular tear film and measuring TFLT can be used in the diagnosis of the tear film, including but not limited to lipid layer and aqueous layer deficiencies. These characteristics may be the cause or contributing factor to a patient experiencing dry eye syndrome (DES).

In this regard, embodiments disclosed herein include a multi-wavelength light source that is controlled to direct light in the visible region to an ocular tear film. The light source may be a Lambertian emitter that provides a uniform or substantially uniform intensity in all directions of emission. The light source is arranged such that light rays emitted from the light source are specularly reflected from the tear film and undergo constructive and destructive optical wave interference interactions (also referred to as “interference interactions”) in the ocular tear film. An imaging device having a detection spectrum that includes the spectrum of the light source is focused on an area(s) of interest on the lipid layer of the tear film. The imaging device captures the interference interactions (i.e., modulation) of specularly reflected light rays from the illuminated tear film coming together by the focusing action of the imaging device in a first image. The imaging device then captures the optical wave interference signals (also referred to as “interference signals”) representing the interference interactions of specularly reflected light from the tear film. The imaging device produces an output signal(s) representative of the interference signal in a first image. The first image may contain an interference signal for a given imaged pixel or pixels of the lipid layer by the imaging device.

The first image can be displayed to a technician or other user. The first image can also be processed and analyzed to measure a TFLT in the area or region of interest of the ocular tear film. In one embodiment, the first image also contains a background signal(s) that does not represent specularly reflected light from the tear film which is superimposed on the interference signal(s). The first image is processed to subtract or substantially subtract out the background signal(s) superimposed upon the interference signal to reduce error before being analyzed to measure TFLT. This is referred to as “background subtraction” in the present disclosure. The separate background signal(s) includes returned captured light that is not specularly reflected from the tear film and thus does not contain optical wave interference information (also referred to as “interference information”). For example, the background signal(s) may include stray, ambient light entering into the imaging device, scattered light from the patient's face and eye structures outside and within the tear film as a result of ambient light and diffuse illumination by the light source, and eye structure beneath the tear film, and particularly contribution from the extended area of the source itself. The background signal(s) adds a bias (i.e., offset) error to the interference signal(s) thereby reducing interference signal strength and contrast. This error can adversely influence measurement of TFLT. Further, if the background signal(s) has a color hue different from the light of the light source, a color shift can also occur to the captured optical wave interference (also referred to as “interference”) of specularly reflected light thus introducing further error.

In this regard in one embodiment, an apparatus for imaging an ocular tear film is disclosed. The apparatus includes a control system configured to receive at least one first image containing optical wave interference of specularly reflecting light in a first polarization plane along with a background signal from a region of interest (ROI, also referred to as area of interest) of the ocular tear film captured by an imaging device while illuminated by the multi-wavelength light source. The control system is also configured to receive at least one second image containing the background signal in a second polarization plane perpendicular or substantially perpendicular to the first polarization plane from the ROI of the ocular tear film captured by an imaging device. In this manner, an imaging device captures background signal(s) in a second image that is representative of the signal which is superimposed on the interference of the specularly reflecting light from the tear film in the first image. The second image is subtracted from the first image to produce a resulting image having isolated interference signal components. The resulting image can then be displayed on a visual display to be analyzed by a technician and/or processed and analyzed to measure a TFLT. One non-limiting benefit of the apparatus is that it allows capturing the at least one second image containing the background signal in a second polarization plane perpendicular or substantially perpendicular to the first polarization plane from the ROI of the ocular tear film. As a result, the background signal is isolated from the interference of the specularly reflecting light from the tear film. Thus, a background offset captured in the at least one first image is removed or reduced from at least one resulting image generated by the subtraction of the at least one second image from the at least one first image.

In another embodiment, a method of imaging an ocular tear film is disclosed. The disclosed method involves illuminating the ROI of an ocular tear film with the multi-wavelength light source. The method includes capturing optical wave interference of specularly reflected light in a first polarization plane including a background signal from the ROI of the ocular tear film while illuminated by the multi-wavelength light source in at least one image by an imaging device. The method also includes capturing the background signal in a second polarizing plane perpendicular or substantially perpendicular to the first polarization plane from the ROI of the ocular tear film in at least one second image by an imaging device. The method also includes subtracting the at least one second image from the at least one first image to generate at least one resulting image containing the optical wave interference of specularly reflected light from the ROI of the ocular tear film with the background signal removed. Capturing the at least one second image containing the background signal in a second polarization plane perpendicular or substantially perpendicular to the first polarization plane from the ROI of the ocular tear film can isolate the background signal from the interference of the specularly reflecting light from the ocular tear film. In this manner, a background offset captured in the at least one first image is removed or reduced from at least one resulting image generated by the subtraction of the at least one second image from the at least one first image.

After the interference of the specularly reflected light is captured and a resulting image containing the interference signal is produced from any method or device disclosed in this disclosure, the resulting image can also be pre-processed before being processed and analyzed to measure TFLT. Pre-processing can involve performing a variety of methods to improve the quality of the resulting signal, including but not limited to detecting and removing eye blinks or other signals in the captured images that hinder or are not related to the tear film. After pre-processing, the interference signal or representations thereof can be processed to be compared against a tear film layer interference model to measure TFLT. The interference signal can be processed and converted by the imaging device into digital red-green-blue (RGB) component values which can be compared to RGB component values in a tear film interference model to measure TFLT on an image pixel-by-pixel basis. The tear film interference model is based on modeling the lipid layer of the tear film in various thicknesses and mathematically or empirically observing and recording resulting interference interactions of specularly reflected light from the tear film model when illuminated by the light source and detected by a camera (imaging device).

In a tear film interference model, the lipid layer is modeled of various LLTs to observe interference interactions resulting from the various LLTs. The aqueous layer may be modeled in the tear film interference model to be of an infinite, minimum, or varying thickness. If the aqueous layer is modeled to be of an infinite thickness, the tear film interference model assumes no specular reflections occur from the aqueous-to-mucin layer transition. If the aqueous layer is modeled to be of a certain minimum thickness (˜>2 μm e.g.), the effect of specular reflection from the aqueous-to-mucin layer transition may be considered in the resulting interference. In either case, the tear film interference model is a 2-wave tear film interference model to represent the interference between specularly reflected light from the air-to lipid layer transition and the lipid-to-aqueous layer transition. Thus, a 2-wave tear film interference model will include one-dimension of data comprised of interference interactions corresponding to the various LLTs. In this case, to measure LLT the interference interactions in the interference signal representing specularly reflected light from the tear film produced by the imaging device are compared to the interference patterns in the tear film interference model. However, if the aqueous layer is also modeled to be of varying ALTs, the tear film interference model will be a 3-wave tear film interference model. The 3-wave tear film interference model will include interference between the air-to lipid layer, lipid-to-aqueous layer, and aqueous-to-mucus/cornea layer transitions. As a result, a 3-wave tear film interference model will include two-dimensions of data comprised of interference interactions corresponding to various LLT and ALT combinations. In this case, to measure LLT and/or ALT the interference interactions from the interference signal representing specularly reflected light from the tear film produced by the imaging device can be compared to interference interactions in the 3-wave tear film interference model.

The tear film interference model can be a theoretical tear film interference model where the light source and the tear film layers are modeled mathematically. The tear film layers may be mathematically modeled by modeling the tear film layers after certain biological materials. Interference interactions from the mathematically modeled light source illuminating the mathematically modeled tear film and received by the mathematically modeled camera are calculated and recorded for varying TFLTs. Alternatively, the tear film interference model can be based on a biological or phantom tear film model comprised of biological or phantom tear film layers. The actual light source is used to illuminate the biological or phantom tear film model and interference interactions representing interference of specularly reflected light are empirically observed and recorded for various TFLTs using the actual camera.

Those skilled in the art will appreciate the scope of the present disclosure and realize additional aspects thereof after reading the following detailed description of the preferred embodiments in association with the accompanying drawing figures.

BRIEF DESCRIPTION OF THE DRAWINGS

The patent or application file contains at least one drawing executed in color. Copies of this patent or patent application publication with color drawing(s) will be provided by the Office upon request and payment of the necessary fee.

The accompanying drawing figures incorporated in and forming a part of this specification illustrate several aspects of the disclosure, and together with the description serve to explain the principles of the disclosure.

FIG. 1 is a side view of an exemplary eye showing the three layers of the tear film in exaggerated form;

FIG. 2 is a front view of an exemplary eye showing the lacrimal and accessory tear glands that produce aqueous in the eye;

FIG. 3 illustrates exemplary upper and lower eyelids showing the meibomian glands contained therein;

FIGS. 4A through 4H illustrate relationships between light waves, beam splitters, and polarizers;

FIG. 5 illustrates a general principle of operation for embodiments of the present disclosure;

FIGS. 6A and 6B illustrate an exemplary light source and imaging device to facilitate discussion of illumination of the tear film and capture of interference interactions of specularly reflected light from the tear film;

FIG. 7 illustrates (in a microscopic section view) exemplary tear film layers to illustrate how light rays can specularly reflect from various tear film layer transitions;

FIG. 8 is a flowchart of an exemplary process that incorporates alternating polarizers for obtaining one or more interference signals from images of a tear film representing specularly reflected light from the tear film with background signal subtracted or substantially subtracted;

FIG. 9 illustrates an exemplary first image focused on a lipid layer of a tear film and capturing interference interactions of specularly reflected light from an area or region of interest of the tear film;

FIG. 10 illustrates an exemplary second image focused on the lipid layer of the tear film in FIG. 9 and capturing background signal when illuminated by the light source;

FIG. 11 illustrates an exemplary image of the tear film when background signal captured in the second image of FIG. 10 is subtracted from the first image of FIG. 9;

FIG. 12 is a perspective view of an exemplary ocular surface interferometry (OSI) device for illuminating and imaging a patient's tear film, displaying images, analyzing the patient's tear film, and generating results from the analysis of the patient's tear film;

FIG. 13 is a side view of the OSI device of FIG. 12 illuminating and imaging the eye and tear film;

FIG. 14A is a side view of an exemplary video camera and illuminator with a rotatable polarizer;

FIG. 14B is a top view of the video camera and illuminator in FIG. 14A with the rotatable polarizer;

FIG. 15 is a flowchart of an exemplary process that employs a rotatable polarizer for obtaining one or more interference signals from images of a tear film representing specularly reflected light from the tear film with background signal subtracted or substantially subtracted;

FIG. 16 is a top view of the illumination device provided in the OSI device of FIGS. 14A and 14B illuminating the tear film with the video camera capturing images of the patient's tear film;

FIG. 17 is a perspective view of an exemplary printed circuit board (PCB) with a plurality of light emitting diodes (LED) provided in the illumination device of the OSI device in FIGS. 14A and 14B to illuminate the tear film;

FIG. 18 is a perspective view of the illumination device and housing in the OSI device of FIGS. 14A and 14B;

FIG. 19A is a side view of an exemplary OSI device with a polarizer wheel having a plurality of polarizers;

FIG. 19B is a top view of the OSI device in FIG. 19A with the polarizer wheel having a plurality of polarizers;

FIG. 20 is a flowchart of an exemplary process that employs the polarizer wheel in FIGS. 19A and 19B for obtaining one or more interference signals from images of a tear film representing specularly reflected light from the tear film with background signal subtracted or substantially subtracted;

FIG. 21A is a side view of an exemplary OSI device employing a dual imager, beam splitter, and individual fixed polarizers configuration;

FIG. 21B is a top view of the OSI device in FIG. 21A in the dual imager, beam splitter, and individual fixed polarizers configuration;

FIG. 22 is a flow chart of an exemplary process for the OSI device that incorporates the dual imager, beam splitter and individual fixed polarizers configuration in FIGS. 21A and 21B;

FIG. 23A is a side view of an exemplary OSI device employing a dual imager and polarizing beam splitter configuration;

FIG. 23B is a top view of the OSI device in FIG. 23A employing the dual imager and polarizing beam splitter configuration;

FIG. 24A is a side view of an exemplary OSI device with the dual imager and polarizing beam splitter configuration that also includes a polarizer in the illumination path of the illuminator;

FIG. 24B is a top view of the OSI device in FIG. 24A employing the dual imager and polarizing beam splitter that also includes a polarizer in the illumination path of the illuminator;

FIG. 25A illustrates an exemplary system diagram of a control system and supporting components that can include the exemplary OSI devices of FIGS. 6A, 6B, 12, 13, 14A, 14B, 19A, 19B, 21A, 21B, 23A, 23B, 24A, and 24B;

FIG. 25B is a flowchart illustrating an exemplary overall processing that can be employed by the OSI devices of FIGS. 6A, 6B, 12, 13, 14A, 14B, 19A, 19B, 21A, 21B, 23A, 23B, 24A, and 24B having systems components according to the exemplary system diagram of the OSI device in FIG. 25A;

FIG. 26 is a flowchart illustrating exemplary pre-processing steps performed on the combined first and second images of a patient's tear film before measuring tear film layer thickness (TFLT);

FIG. 27 is an exemplary graphical user interface (GUI) for controlling imaging, pre-processing, and post-processing settings that can be employed by the OSI devices of FIGS. 6A, 6B, 12, 13, 14A, 14B, 19A, 19B, 21A, 21B, 23A, 23B, 24A, and 24B;

FIG. 28 illustrates an example of a subtracted image in an area or region of interest of a tear film containing specularly reflected light from the tear film overlaid on top of a background image of the tear film;

FIGS. 29A and 29B illustrate exemplary threshold masks that may be used to provide a threshold function during pre-processing of a resulting image containing specularly reflected light from a patient's tear film;

FIG. 30 illustrates an exemplary image of FIG. 28 after a threshold pre-processing function has been performed leaving interference of the specularly reflected light from the patient's tear film;

FIG. 31 illustrates an exemplary image of the image of FIG. 30 after erode and dilate pre-processing functions have been performed on the image;

FIG. 32 illustrates an exemplary histogram used to detect eye blinks and/or eye movements in captured images or frames of a tear film;

FIG. 33 illustrates an exemplary process for loading an International Colour Consortium (ICC) profile and tear film interference model into the OSI devices of FIGS. 6A, 6B, 12, 13, 14A, 14B, 19A, 19B, 21A, 21B, 23A, 23B, 24A, and 24B;

FIG. 34 illustrates a flowchart providing an exemplary visualization system process for displaying images of a patient's tear film on a display in the OSI devices of FIGS. 6A, 6B, 12, 13, 14A, 14B, 19A, 19B, 21A, 21B, 23A, 23B, 24A, and 24B;

FIGS. 35A-35C illustrate exemplary images of a tear film with a pattern of interference interactions from specularly reflected light from the tear film displayed on a display;

FIG. 36 illustrates an exemplary post-processing system that may be provided in the OSI devices of FIGS. 6A, 6B, 12, 13, 14A, 14B, 19A, 19B, 21A, 21B, 23A, 23B, 24A, and 24B;

FIG. 37A illustrates an exemplary 3-wave tear film interference model based on a 3-wave theoretical tear film model to correlate different observed interference color with different lipid layer thicknesses (LLTs) and aqueous layer thicknesses (ALTs);

FIG. 37B illustrates another exemplary 3-wave tear film interference model based on a 3-wave theoretical tear film model to correlate different observed interference color with different lipid layer thicknesses (LLTs) and aqueous layer thicknesses (ALTs);

FIG. 38 is another representation of the 3-wave tear film interference model of FIG. 37 with normalization applied to each red-green-blue (RGB) color value individually;

FIG. 39 is an exemplary histogram illustrating results of a comparison of interference interactions from the interference signal of specularly reflected light from a patient's tear film to the 3-wave tear film interference model of FIGS. 37 and 38 for measuring TFLT of a patient's tear film;

FIG. 40 is an exemplary histogram plot of distances in pixels between RGB color value representation of interference interactions from the interference signal of specularly reflected light from a patient's tear film and the nearest distance RGB color value in the 3-wave tear film interference model of FIGS. 37 and 38;

FIG. 41 is an exemplary threshold mask used during pre-processing of the tear film images;

FIG. 42 is an exemplary three-dimensional (3D) surface plot of the measured LLT and ALT thicknesses of a patient's tear film;

FIG. 43 is an exemplary image representing interference interactions of specularly reflected light from a patient's tear film results window based on replacing a pixel in the tear film image with the closest matching RGB color value in the normalized 3-wave tear film interference model of FIG. 38;

FIG. 44 is an exemplary TFLT palette curve for a TFLT palette of LLTs plotted in RGB space for a given ALT in three-dimensional (3D) space;

FIG. 45 is an exemplary TFLT palette curve for the TFLT palette of FIG. 44 with LLTs limited to a maximum LLT of 240 nm plotted in RGB space for a given ALT in three-dimensional (3D) space;

FIG. 46 illustrates the TFLT palette curve of FIG. 45 with an acceptable distance to palette (ADP) filter shown to determine tear film pixel values having RGB values that correspond to ambiguous LLTs;

FIG. 47 is an exemplary login screen to a user interface system for controlling and accessing the OSI devices of FIGS. 6A, 6B, 12, 13, 14A, 14B, 19A, 19B, 21A, 21B, 23A, 23B, 24A, and 24B;

FIG. 48 illustrates an exemplary interface screen for accessing a patient database interface in the OSI devices of FIGS. 6A, 6B, 12, 13, 14A, 14B, 19A, 19B, 21A, 21B, 23A, 23B, 24A, and 24B;

FIG. 49 illustrates a patient action control box for selecting to either capture new tear film images of a patient in the patient database or view past captured images of the patient from the OSI devices of FIGS. 6A, 6B, 12, 13, 14A, 14B, 19A, 19B, 21A, 21B, 23A, 23B, 24A, and 24B;

FIG. 50 illustrates a viewing interface for viewing a patient's tear film either captured in real-time or previously captured by the OSI devices of FIGS. 6A, 6B, 12, 13, 14A, 14B, 19A, 19B, 21A, 21B, 23A, 23B, 24A, and 24B;

FIG. 51 illustrates a tear film image database for a patient;

FIG. 52 illustrates a view images GUI screen showing an overlaid image of interference interactions of the interference signals from specularly reflected light from a patient's tear film overtop an image of the patient's eye for both the patient's left and right eyes side by side;

FIG. 53 illustrates the GUI screen of FIG. 52 with the images of the patient's eye toggled to show only the interference interactions of the interference signals from specularly reflected light from a patient's tear film;

FIG. 54 is a flow chart that illustrates step-by-step processing of a polarization subtraction technique of the present disclosure;

FIGS. 55A-F are examples of the images selected to implement the step-by-step processing of FIG. 54;

FIGS. 56A-56D are examples of how a surface of an eye can be segmented for imaging and analysis purposes according to one or more of the techniques described in the present disclosure;

FIG. 57 is a flowchart of an exemplary process of capturing an image(s) of an area of interest of an ocular tear film according to one embodiment;

FIG. 58 is a flowchart of an exemplary process for calculating a break-up time of an ocular tear film according to one embodiment;

FIG. 59 is a flowchart of an exemplary process for calculating a break-up time of an ocular tear film using a fluorescein break-up time (FBUT) technique with a cobalt blue field according to one embodiment;

FIG. 60 is a flowchart of an exemplary process for calculating a Tear Thinning Time (TTT) of an ocular tear film according to one embodiment;

FIG. 61 is a flowchart of an exemplary process for calculating a Non Invasive Break-up Time (NIBUT) of an ocular tear film according to one embodiment, based on a disappearance of a lipid layer during a non-blink;

FIGS. 62A and 62B is a flowchart of an exemplary process in which an imaging device may be programmed to look at alternating segments of a surface of a cornea of the an eye, where the imaging device may be configured to alternate imaging the segments of the cornea with a first light source and a second light source until a threshold event occurs;

FIG. 63A illustrates the eye during a blink;

FIG. 63B illustrates the eye with an increased aperture due to an upper gaze by a patent; and

FIG. 63C illustrates an exemplary technique of how to measure an amplitude of a blink of an eye based on the distance an upper eyelid of the eye travels during a blink with respect to a pupil of the eye.

DETAILED DESCRIPTION

The embodiments set forth below represent the necessary information to enable those skilled in the art to practice the disclosure and illustrate the best mode of practicing the disclosure. Upon reading the following description in light of the accompanying drawing figures, those skilled in the art will understand the concepts of the disclosure and will recognize applications of these concepts not particularly addressed herein. It should be understood that these concepts and applications fall within the scope of the disclosure and the accompanying claims.

Embodiments of the detailed description include devices, systems, and methods for determining tear film break-up time and for detecting eyelid margin contact and blink rates, particularly for diagnosing, measuring, and/or analyzing dry eye conditions and symptoms. The apparatus and methods for determining tear film break-up time and for detecting eyelid margin contact and blink rates, particularly for diagnosing, measuring, and/or analyzing dry eye conditions and symptoms may employ ocular surface interferometry (OSI) devices or other imaging and display devices capable of imaging and displaying a picture of a patient's eye during tear film break-up time and blink rate related procedures.

Before discussing embodiments of determining tear film break-up time and for detecting eyelid margin contact and blink rates, exemplary OSI devices that can be employed to image, process, measure, and/or display tear film break-up time and for detecting eyelid margin contact and blink rates, are first described in detail below

In this regard, embodiments of the detailed description include ocular surface interferometry (OSI) devices, systems, and methods for imaging an ocular tear film and/or measuring a tear film layer thickness (TFLT) of an ocular tear film. The OSI devices, systems, and methods can be used to measure the thickness of the lipid layer component (LLT) and/or the aqueous layer component (ALT) of the ocular tear film. “TFLT” as used herein includes LLT, ALT, or both LLT and ALT. “Measuring TFLT” as used herein includes measuring LLT, ALT, or both LLT and ALT. Imaging the ocular tear film and measuring TFLT can be used in the diagnosis of a patient's tear film, including but not limited to lipid layer and aqueous layer deficiencies. These characteristics may be the cause or contributing factor to a patient experiencing dry eye syndrome (DES).

In this regard, embodiments disclosed herein include a multi-wavelength light source that is controlled to direct light in the visible region to an ocular tear film. The light source may be a Lambertian emitter that provides a uniform or substantially uniform intensity in all directions of emission. The light source is arranged such that light rays emitted from the light source are specularly reflected from the tear film and undergo constructive and destructive optical wave interference interactions (also referred to as “interference interactions”) in the ocular tear film. In some embodiments, the light source and an imaging device having a detection spectrum that includes the spectrum of the light source is focused on an area(s) of interest on the lipid layer of the tear film. The imaging device captures the interference interactions (i.e., modulation) of specularly reflected light rays from the illuminated tear film coming together by the focusing action of the imaging device in a first image. The imaging device then captures the optical wave interference signals (also referred to as “interference signals”) representing the interference interactions of specularly reflected light from the tear film. The imaging device produces an output signal(s) representative of the interference signal in a first image. The first image may contain an interference signal for a given imaged pixel or pixels of the lipid layer by the imaging device.

The first image can be displayed to a technician or other user. The first image can also be processed and analyzed to measure a TFLT in the area or region of interest of the ocular tear film. In one embodiment, the first image also contains a background signal(s) that does not represent specularly reflected light from the tear film which is superimposed on the interference signal(s). The first image is processed to subtract or substantially subtract out the background signal(s) superimposed upon the interference signal to reduce error before being analyzed to measure TFLT. This is referred to as “background subtraction” in the present disclosure. The separate background signal(s) includes returned captured light that is not specularly reflected from the tear film and thus does not contain optical wave interference information (also referred to as “interference information”). For example, the background signal(s) may include stray, ambient light entering into the imaging device, scattered light from the face and eye structures outside and within the tear film as a result of ambient light and diffuse illumination by the light source, and eye structure beneath the tear film, and particularly contribution from the extended area of the source itself. The background signal(s) adds a bias (i.e., offset) error to the interference signal(s) thereby reducing interference signal strength and contrast. This error can adversely influence measurement of TFLT. Further, if the background signal(s) has a color hue different from the light of the light source, a color shift can also occur to the captured optical wave interference (also referred to as “interference”) of specularly reflected light thus introducing further error.

In this regard in one embodiment, an apparatus for imaging an ocular tear film is disclosed. The apparatus includes a control system configured to receive at least one first image containing optical wave interference of specularly reflecting light in a first polarization plane along with a background signal from a region of interest (ROI, also referred to as area of interest) of the ocular tear film captured by an imaging device while illuminated by the multi-wavelength light source. The control system is also configured to receive at least one second image containing the background signal in a second polarization plane perpendicular or substantially perpendicular to the first polarization plane from the ROI of the ocular tear film captured by an imaging device. In this manner, an imaging device captures background signal(s) in a second image that is representative of the signal which is superimposed on the interference of the specularly reflecting light from the tear film in the first image. The second image is subtracted from the first image to produce a resulting image having isolated interference signal components. The resulting image can then be displayed on a visual display to be analyzed by a technician and/or processed and analyzed to measure a TFLT. One non-limiting benefit of the apparatus is that it allows capturing the at least one second image containing the background signal in a second polarization plane perpendicular or substantially perpendicular to the first polarization plane from the ROI of the ocular tear film. As a result, the background signal is isolated from the interference of the specularly reflecting light from the tear film. Thus, a background offset captured in the at least one first image is removed or reduced from at least one resulting image generated by the subtraction of the at least one second image from the at least one first image.

In another embodiment, a method of imaging an ocular tear film is disclosed. The disclosed method involves illuminating the ROI of an ocular tear film with the multi-wavelength light source. The method include capturing optical wave interference of specularly reflected light in a first polarization plane including a background signal from the ROI of the ocular tear film while illuminated by the multi-wavelength light source in at least one image by an imaging device. The method also includes capturing the background signal in a second polarizing plane perpendicular or substantially perpendicular to the first polarization plane from the ROI of the ocular tear film in at least one second image by an imaging device. The method also includes subtracting the at least one second image from the at least one first image to generate at least one resulting image containing the optical wave interference of specularly reflected light from the ROI of the ocular tear film with the background signal removed. Capturing the at least one second image containing the background signal in a second polarization plane perpendicular or substantially perpendicular to the first polarization plane from the ROI of the ocular tear film can isolate the background signal from the interference of the specularly reflecting light from the ocular tear film. In this manner, a background offset captured in the at least one first image is removed or reduced from at least one resulting image generated by the subtraction of the at least one second image from the at least one first image.

Before discussing the particular embodiments of the present disclosure, a discussion of the electromagnetic nature of light waves is provided with regard to FIGS. 4A-4H. Light waves, like all electromagnetic waves, propagate with an oscillating electric field that generates an oscillating magnetic field that regenerates the oscillating electric field and so on. Moreover, light waves exhibit a property known as polarization. For example, when the orientation of the oscillating electric field is in a fixed plane in space, the light wave is a plane-polarized wave. When the plane of the electric field rotates as a light wave propagates spirally through space, the light wave is a circularly or elliptically polarized light wave. Furthermore, light made up of many light waves that are randomly polarized is referred to as unpolarized light, since there is no single polarization plane for unpolarized light.

Optical filters known as polarizers allow unimpeded transmission of light waves having a single polarization-plane. Any type of polarizer may be employed in the embodiments discussed below. For example, a linear polarizer may be employed to reduce the intensity of a background signal(s). An exemplary linear polarizer has a polarization axis that typically extends across the polarizer. Light waves that impinge upon the linear polarizer with a polarization-plane that is parallel to the polarization axis of the polarizer will pass through the polarizer unimpeded. In contrast, light waves that impinge upon the linear polarizer with polarization-planes that are not parallel to the polarization-plane of the polarizer will be impeded. As another non-limiting example, a circular polarizer or an elliptical polarizer can be employed in any of the embodiments below to reduce the intensity of a background signal(s). Circular polarizers and/or elliptical polarizers may also be usable to prevent unintentional secondary specular reflections in embodiments that use beam splitters. An exemplary circular polarizer may comprise two components. One component is a linear polarizer such as the exemplary polarizer described above that passes light waves in one polarization-plane. The other component is a quarter wave plate that transforms light waves passing through the linear polarizer in one polarization-plane into circularly polarized light waves. Exemplary elliptical polarizers may comprise the same components as circular polarizers. An elliptical polarizer is configured such that it transforms the light passing through the linear polarizer in one polarization-plane into elliptically polarized light. Elliptically polarized light has unequal electric field amplitudes.

The intensity of a light wave is related to its electric field amplitude. The degree to which the intensity of a light wave is reduced by a polarizer depends on the angle between the polarization plane of the light wave and the polarization axis of the polarizer. According to Malus' law, a light wave impinging on a polarizer will be reduced in amplitude in proportion to the cosine of the angle between the polarization plane of the light wave and the polarization axis of the polarizer. A light wave that has a polarization plane that is parallel with the polarization axis will have a 0° angle between its polarization plane and the polarization axis of the polarizer. Since the cosine of 0° is one, Malus' law ideally predicts no reduction of light intensity for a light wave that has a polarization plane that is parallel with the polarization axis. In contrast, Malus' law ideally predicts no transmission through a polarizer for a light wave that impinges on the polarizer with a polarization plane that is perpendicular to the polarization axis of the polarizer since the cosine of 90° is zero.

When unpolarized light impinges on a polarizer, the overall intensity of the light is reduced by at least 50% due to the summations of amplitude reductions due to Malus' law as applied to individual light waves having random polarization planes impinging on the polarizer. Light that is transmitted through the polarizer becomes polarized such that the light has a polarization plane that is parallel with the polarization axis of the polarizer.

Light intensity is proportional to the square of the amplitude. Therefore, the intensity of light transmitted through the polarizer from a non-polarized light source is ideally 25%. However, modern polarizers are not perfect, which results in additional losses of intensity for the transmitted light due to absorption, scattering and other intensity degrading effects.

In this regard, FIGS. 4A through 4H illustrate relationships between light waves, polarizers and beam splitters. Referring to FIG. 4A, a polarizer 30 has a polarization axis 32 that is oriented in a direction indicated by a polarization axis arrow. A light wave 34 impinging on the polarizer 30 is in a polarization plane that is parallel to the polarization axis 32 of the polarizer 30. As a result, the light wave 34 is transmitted unimpeded through the polarizer 30.

In contrast, FIG. 4B shows the polarizer 30 rotated such that the polarization axis 32 is perpendicular to the polarization plane of the light wave 34 as indicated by the polarization axis arrow. In this case, none of the light wave 34 will be transmitted through the polarizer 30. FIG. 4C and FIG. 4D represent the same conditions as FIG. 4A and FIG. 4B respectively. However, the polarization plane of light wave 34 is represented by double headed arrows 36 instead of the sine wave representation used to represent light wave 34 in FIGS. 4A and 4B.

FIG. 4E illustrates a condition wherein the light wave 34 impinges upon the polarizer 30 when the difference in the angle between the polarization plane of the light wave 34 and the polarization axis 32 is intermediate of parallel and perpendicular. In this case, a portion of the light wave 34 is transmitted through the polarizer 30. The portion of light wave 34 that is transmitted through the polarizer 30 obtains a polarization plane that is parallel to the polarization axis 32 of the polarizer 30. The intensity of the transmitted portion of the light wave 34 is reduced relative to the intensity of the light wave 34 that is impinging on the polarizer 30. The relative intensity of the light wave 34 is represented by the relative difference in length of the double-headed arrows 36.

FIG. 4F illustrates a light beam 38 that is shown impinging on the polarizer 30. The light beam 38 is made up of a plurality of light waves that are in random polarization planes. In this example, the light beam 38 includes the light wave 34 having a polarization plane that aligns with the polarization axis 32 of the polarizer 30. As a result of the alignment, the light wave 34 is transmitted through the polarizer 30.

FIG. 4G illustrates a specular reflection and a refraction of the light wave 34 as the light wave 34 impinges on the minor-like surface of a polarizing beam splitter 40. In the example of FIG. 4G, the light wave 34 has a first polarization plane as it arrives at polarizing beam splitter 40. A first portion 42 of the light wave 34 specularly reflects from the polarizing beam splitter 40 in a second polarization plane that is perpendicular to the first polarization plane of the impinging light wave 34. A second portion 44 of the light wave 34 is refracted by the polarizing beam splitter 40. The second portion 44 of the light wave 34 maintains the first polarization plane of the impinging light wave 34.

FIG. 4H illustrates a specular reflection and a refraction of the light wave 34 that is one of a plurality of light waves that make up the light beam 38 as it impinges upon the polarizing beam splitter 40. As in the previous case, the light wave 34 in the first polarization plane is split into the first portion 42 and the second portion 44. As before, the first portion 42 of the light wave 34 is specularly reflected from the polarizing beam splitter 40 in a polarization plane that is perpendicular to the first polarization plane of the impinging light wave 34. As before, the second portion 44 of the light wave 34 maintains the first polarization plane of the impinging light wave 34.

FIG. 5 illustrates exemplary devices that can be provided in an OSI device according to a first embodiment. An optical system 46 is made up of a light source 48, a non-polarizing beam splitter 50, a first polarizer 52 having a polarization axis 54 and a second polarizer 56 having a polarization axis 58. In the exemplary case of FIG. 5, light 60 emitted from the light source 48 is unpolarized. However, the exemplary case of FIG. 5 should not be viewed as limiting the present disclosure to unpolarized illumination, since at least one embodiment of the present disclosure utilizes a polarizer in the illumination path of a light source 48. The unpolarized light is directed from the light source 48 to a target 62, which in the case of the present disclosure is a tear film covering the human eye. The target 62 reflects the unpolarized light to the non-polarizing beam splitter 50. After reflecting from the target 62, the unpolarized light 60 comprises an undesirable background signal that will be eliminated or reduced from images captured by the imaging device by processing, techniques discussed later in the present disclosure.

A portion of the unpolarized light 60 reflects from the non-polarizing beam splitter 50 to the first polarizer 52. A portion of the unpolarized light 60 having a polarization plane that aligns with the polarization axis 54 passes through the first polarizer 52 unimpeded. A summation of other light waves making up the unpolarized light 60 having polarization planes that are not perpendicular to the polarization axis 54 are also transmitted through the first polarizer 52 with reduced intensity. Light waves 64 that are transmitted through the first polarizer 52 each have a polarization plane that is parallel to the polarization axis 54.

A refracted portion of the unpolarized light 60 is directed to the second polarizer 56. Similar to the light interaction with the first polarizer 52, a portion of the unpolarized light 60 having a polarization plane that aligns with the polarization axis 58 passes through the second polarizer 56 unimpeded. A summation of other light waves making up the unpolarized light 60 having polarization planes that are not perpendicular to the polarization axis 58 are also transmitted through the second polarizer 56 with reduced intensity. Light waves 66 that are transmitted through the second polarizer 56 each have a polarization plane that is parallel to the polarization axis 58.

Another portion of the unpolarized light 60 emitted from the light source 48 is specularly reflected from the target 62 such that a polarized light 68 is directed to the non-polarizing beam splitter 50. A first portion of the polarized light 68 is specularly reflected from the non-polarizing beam splitter 50 so that the polarized light is re-polarized in a polarization plane that is perpendicular to the polarization axis 54 of the first polarizer 52. In this way, the polarized light 68 that is specularly reflected from the target 62 is practically prevented from passing through the first polarizer 52. In contrast, a portion of the polarized light 68 that is refracted through the non-polarizing beam splitter 50 retains the polarization plane of the polarized light 68 as it specularly reflects from the target 62. The polarization axis 58 of the second polarizer 56 is aligned such that the portion of the specularly reflected light 84 passes through the second polarizer 56 unimpeded.

Against the discussion above, embodiments disclosed herein and discussed in more detail below include ocular surface interferometry (OSI) devices, systems, and methods for measuring a tear film layer thickness (TFLT) of the ocular tear film. The OSI devices, systems, and methods can be used to measure the thickness of the lipid layer component (LLT) and/or the aqueous layer component (ALT) of the ocular tear film. “TFLT” as used herein includes LLT, ALT, or both LLT and ALT. “Measuring TFLT” as used herein includes measuring LLT, ALT, or both LLT and ALT. Measuring TFLT can be used in the diagnosis of an ocular tear film, including but not limited to lipid layer and aqueous layer deficiencies. These characteristics may be the cause or contributing factor to a mammalian experiencing dry eye syndrome (DES).

In this regard, embodiments disclosed herein include a light source that is controlled to direct light in the visible region to an ocular tear film. For example, the light source may be a Lambertian emitter that provides a uniform or substantially uniform intensity in all directions of emission. The light source is arranged such that light rays emitted from the light source are specularly reflected toward an imaging device from the tear film and undergo constructive and destructive interference interactions in the ocular tear film. An imaging device having a detection spectrum that includes the spectrum of the light source is focused on an area(s) of interest on the lipid layer of the tear film. The imaging device captures a first image of the interference interactions (i.e., modulation) of specularly reflected light rays from the illuminated tear film coming together by the focusing action of the imaging device. The imaging device then captures the interference signals representing the interference interactions of specularly reflected light from the tear film. The imaging device produces an output signal(s) representative of the interference signal in a first image. The first image may contain an interference signal for a given imaged pixel or pixels of the lipid layer by the imaging device. The output signal(s) can be processed and analyzed to measure a TFLT in the area or region of interest of the ocular tear film.

OSI Device Employing Alternating Polarizers

In this regard, FIGS. 6A and 6B illustrate a general embodiment of an ocular surface interferometry (OSI) device 70. Other embodiments will be described later in this application. In general, the OSI device 70 is configured to illuminate a patient's ocular tear film, capture images of interference interactions of specularly reflected light from the ocular tear film, and process and analyze the interference interactions to measure TFLT. As shown in FIG. 6A, the exemplary OSI device 70 positioned in front of one of the patient's eye 72 is shown from a side view. A top view of the patient 74 in front of the OSI device 70 is illustrated in FIG. 6B. The ocular tear film of a patient's eyes 72 is illuminated with a light source 76 (also referred to herein as “illuminator 76”) and comprises a large area light source having a spectrum in the visible region adequate for TLFT measurement and correlation to dry eye. The illuminator 76 can be a white or multi-wavelength light source.

In this embodiment, the illuminator 76 is a Lambertian emitter and is adapted to be positioned in front of the eye 72 on a stand 78. As employed herein, the terms “Lambertian surface” and “Lambertian emitter” are defined to be a light emitter having equal or substantially equal (also referred to as “uniform” or substantially uniform) intensity in all directions. This allows the imaging of a uniformly or substantially uniformly bright tear film region for TFLT, as discussed in more detail in this disclosure. The illuminator 76 comprises a large surface area emitter, arranged such that rays emitted from the emitter are specularly reflected from the ocular tear film and undergo constructive and destructive interference in tear film layers therein. An image of the patient's 74 lipid layer is the backdrop over which the interference image is seen and it should be as spatially uniform as possible.

An imaging device 80 is included in the OSI device 70 and is employed to capture interference interactions of specularly reflected light from the patient's 74 ocular tear film when illuminated by the illuminator 76. The imaging device 80 may be a still or video camera, or other device that captures images and produces an output signal representing information in captured images. The output signal may be a digital representation of the captured images.

Optical filtering is used to improve isolation of interference interactions of specularly reflected light from the patient's 74 ocular tear film before images of the patient's 74 ocular tear film are captured. In this regard, a first polarizer 52(1) is selectively disposable in an imaging path of the imaging device 80 during the capture of at least one first image. A second polarizer 56(1) is selectively disposable in the imaging path of the imaging device 80 during the capture of at least one second image.

When the first polarizer 52(1) is in front of imaging lens 82, the specularly reflected light 84 from a region of interest (ROI, or the area of interest) of the ocular tear film is allowed to pass or substantially pass to the imaging device 80. Simultaneously, the background signal is reduced before the background signal reaches the imaging device 80. In contrast, when the second polarizer 56(1) is in front of imaging lens 82, the specularly reflected light 84 from the ROI of the ocular tear film is reduced or eliminated before the specularly reflected light 84 reaches the imaging device 80 while passing a portion of the background signal. As a result, a first image captured with the first polarizer 52(1) in front of the imaging lens 82 will include a maximum amount of imagery resulting from the specularly reflected light 84 with a reduced amount of background signal. Moreover, a second image captured with the second polarizer 56(1) in front of the imaging lens 82 will have a minimum amount or none of the specularly reflected light along with a reduced background signal. Consequently, the second image can be subtracted from the first image to generate a resultant image that is predominately comprised of the ocular tear film.

As shown in FIGS. 6A and 6B, the first polarizer 52(1) and the second polarizer 56(1) are alternately translatable into the imaging path of the imaging device 80. In FIG. 6A the translation is shown occurring along the Y-AXIS, whereas in FIG. 6B the translation is shown occurring along the Z-AXIS. It is to be understood that translation of the first polarizer 52(1) and the second polarizer 56(1) along axes intermediate the Y-AXIS and the Z-AXIS may also be available depending on clearances and personal choice.

The geometry of the illuminator 76 can be understood by starting from an imaging lens 82 of the imaging device 80 and proceeding forward to the eye 72 and then to the illuminator 76. The fundamental equation for tracing ray lines is Snell's law, which provides:

n1 Sin Θ₁=n2 Sin Θ₂,

where “n1” and “n2” are the indexes of refraction of two mediums containing the ray, and Θ₁ and Θ₂ is the angle of the ray relative to the normal from the transition surface. As illustrated in FIG. 7, light rays 90 are directed by the illuminator 76 (FIGS. 6A and 6B) to an ocular tear film 92. In the case of specularly reflected light 94 that does not enter a lipid layer 96 and instead reflects from an anterior surface 98 of the lipid layer 96, Snell's law reduces down to Θ₁=Θ₂, since the index of refraction does not change (i.e., air in both instances). Under these conditions, Snell's law reduces to the classical law of reflection such that the angle of incidence is equal and opposite to the angle of reflectance.

Some of the light rays 100 pass through the anterior surface 98 of the lipid layer 96 and enter into the lipid layer 96, as illustrated in FIG. 7. As a result, the angle of these light rays 100 (i.e., Θ₃) normal to the anterior surface 98 of the lipid layer 96 will be different than the angle of the light rays 90 (Θ₁) according to Snell' s law. This is because the index of refraction of the lipid layer 96 is different than the index of refraction of air. Some of the light rays 100 passing through the lipid layer 96 will specularly reflect from the lipid layer-to-aqueous layer transition 102 thereby producing specularly reflected light rays 104. The specularly reflected light rays 94, 104 undergo constructive and destructive interference anterior of the lipid layer 96. The modulations of the interference of the specularly reflected light rays 94, 104 superimposed on the anterior surface 98 of the lipid layer 96 are collected by the imaging device 80 when focused on the anterior surface 98 of the lipid layer 96. Focusing the imaging device 80 on the anterior surface 98 of the lipid layer 96 allows capturing of the modulated interference information at the plane of the anterior surface 98. In this manner, the captured interference information and the resulting calculated TFLT from the interference information is spatially registered to a particular area of the tear film 92 since that the calculated TFLT can be associated with such particular area, if desired.

The thickness of the lipid layer 96 (‘d₁’) is a function of the interference interactions between specularly reflected light rays 94, 104. The thickness of the lipid layer 96 (‘d₁’) is on the scale of the temporal (or longitudinal) coherence of the light source 76. Therefore, thin lipid layer films on the scale of one wavelength of visible light emitted by the light source 76 offer detectable colors from the interference of specularly reflected light when viewed by a camera or human eye. The colors may be detectable as a result of calculations performed on the interference signal and represented as a digital values including but not limited to a red-green-blue (RGB) value in the RGB color space. Quantification of the interference of the specularly reflected light can be used to measure LLT. The thicknesses of an aqueous layer 106 (‘d₂’) can also be determined using the same principle. Some of the light rays 100 (not shown) passing through the lipid layer 96 can also pass through the lipid-to-aqueous layer transition 102 and enter into the aqueous layer 106 specularly reflecting from the aqueous-to-mucin/cornea layer transition 108. These specular reflections also undergo interference with the specularly reflected light rays 94, 104. The magnitude of the reflections from each interface depends on the refractive indices of the materials as well as the angle of incidence, according to Fresnel's equations, and so the depth of the modulation of the interference interactions is dependent on these parameters, thus so is the resulting color.

Turning back to FIGS. 6A and 6B, the illuminator 76 in this embodiment is a broad spectrum light source covering the visible region between about 400 nm to about 700 nm. The illuminator 76 contains an arced or curved housing 86 (see FIG. 6B) into which individual light emitters are mounted, subtending an arc of approximately 130 degrees from the optical axis of the eye 72 (see FIG. 6B). A curved surface may present better uniformity and be more efficient, as the geometry yields a smaller device to generating a given intensity of light. The total power radiated from the illuminator 76 should be kept to a minimum to prevent accelerated tear evaporation. Light entering the pupil can cause reflex tearing, squinting, and other visual discomforts, all of which affect TFLT measurement accuracy.

In order to prevent alteration of the proprioceptive senses and reduce heating of the tear film 92, incident power and intensity on the eye 72 may be minimized and thus, the step of collecting and focusing the specularly reflected light may carried out by the imaging device 80. The imaging device 80 may be a video camera, slit lamp microscope, or other observation apparatus mounted on the stand 78, as illustrated in FIGS. 6A and 6B. Detailed visualization of the image patterns of the tear film 92 involves collecting the specularly reflected light 84 and focusing the specularly reflected light at the lipid layer 96 such that the interference interactions of the specularly reflected light from the ocular tear film are observable.

In operation, the first polarizer 52(1) is translated in front of imaging lens 82 such that the polarization axis 54(1) is parallel or substantially parallel to the polarization plane of the specularly reflected light 84 from a region of interest (ROI) of the ocular tear film. In this manner, the specularly reflected light 84 is allowed to pass or substantially pass to the imaging device 80 while reducing the background signal before the background signal reaches the imaging device 80. Moreover, the second polarizer 56(1) is translated in front of imaging lens 82 such that the polarization axis 58(1) is perpendicular or substantially perpendicular to the polarization plane of the specularly reflected light 84 from the ROI of the ocular tear film. In this manner, the specularly reflected light 84 is reduced or eliminated before the specularly reflected light 84 reaches the imaging device 80 while passing a portion of the background signal.

Against the backdrop of the OSI device 70 in FIGS. 6A and 6B, FIG. 8 illustrates a flowchart discussing how the OSI device 70 can be used to obtain interference interactions of specularly reflected light from the tear film 92, which can be used to measure TFLT. Interference interactions of specularly reflected light from the tear film 92 are first obtained and discussed before measurement of TFLT is discussed. In this embodiment as illustrated in FIG. 8, the process starts by adjusting the patient 74 with regard to an illuminator 76 and an imaging device 80 (block 110). The illuminator 76 is controlled to illuminate the patient's 74 tear film 92. The imaging device 80 is controlled to be focused on the anterior surface 98 of the lipid layer 96 such that the interference interactions of specularly reflected light from the tear film 92 are collected and are observable. Thereafter, the patient's 74 tear film 92 is illuminated by the illuminator 76 (block 112).

The imaging device 80 is then controlled and focused on the lipid layer 96 to collect specularly reflected light from an area or ROI on a tear film as a result of illuminating the tear film with the illuminator 76 in a first image (block 114, FIG. 8). An example of the first image by the illuminator 76 is provided in FIG. 9. As illustrated therein, a first image 130 of a patient's eye 132 is shown that has been illuminated with the illuminator 76. The illuminator 76 and the imaging device 80 may be controlled to illuminate an area or region of interest 134 on a tear film 136 that does not include a pupil 138 of the eye 132 so as to reduce reflex tearing. Reflex tearing will temporarily lead to thicker aqueous and lipid layers, thus temporarily altering the interference signals of specularly reflected light from the tear film 136. As shown in FIG. 9, when the imaging device 80 is focused on an anterior surface 142 of the lipid layer 144 of the tear film 136, interference interactions 140 of the interference signal of the specularly reflected light from the tear film 136 as a result of illumination by the illuminator 76 are captured in the area or region of interest 134 in the first image 130. The interference interactions 140 appear to a human observer as colored patterns as a result of the wavelengths present in the interference of the specularly reflected light from the tear film 136.

However, even though the background signal is reduced by the first polarizer 52(1), a portion of the background signal is also captured in the first image 130. The background signal is added to the specularly reflected light in the area or region of interest 134 and included outside the area or region of interest 134 as well. Background signal is light that is not specularly reflected from the tear film 136 and thus contains no interference information. Background signal can include stray and ambient light entering into the imaging device 80, scattered light from the patient's 74 face, eyelids, and/or eye 132 structures outside and beneath the tear film 136 as a result of stray light, ambient light and diffuse illumination by the illuminator 76, and images of structures beneath the tear film 136. For example, the first image 130 includes the iris of the eye 132 beneath the tear film 136. Background signal adds a bias (i.e., offset) error to the captured interference of specularly reflected light from the tear film 136 thereby reducing its signal strength and contrast. Further, if the background signal has a color hue different from the light of the light source, a color shift can also occur to the interference of specularly reflected light from the tear film 136 in the first image 130. The imaging device 80 produces a first output signal that represents the light rays captured in the first image 130. Because the first image 130 contains light rays from specularly reflected light as well as the background signal, the first output signal produced by the imaging device 80 from the first image 130 will contain an interference signal representing the captured interference of the specularly reflected light from the tear film 136 with a bias (i.e., offset) error caused by the background signal. As a result, the first output signal analyzed to measure TFLT may contain error as a result of the background signal bias (i.e., offset) error.

Thus, in this embodiment, the first output signal generated by the imaging device 80 as a result of the first image 130 is processed to subtract or substantially subtract the background signal from the interference signal to reduce error before being analyzed to measure TFLT. This is also referred to as “background subtraction.” Background subtraction is the process of removing unwanted reflections from images. In this regard, the imaging device 80 is controlled to capture a second image 146 of the tear film 136 as illustrated by example in FIG. 10. However, before the second image 146 is captured, a switch from the first polarizer 52(1) in the first orientation to the second polarizer 56(1) in the second orientation is made (block 116 in FIG. 8). In this way, the second image 146 will contain mostly background signal and when the second image 146 is subtracted from the first image 130 the captured interference of specularly reflected light from the tear film 136 will not be reduced or at least not significantly reduced.

The second image 146 should be captured using the same imaging device 80 settings and focal point as when capturing the first image 130 so that the first image 130 and second images 146 forms corresponding image pairs captured within a short time of each other. The imaging device 80 produces a second output signal containing background signal present in the first image 130 (block 118 in FIG. 8). To eliminate or reduce this background signal from the first output signal, the second output signal is subtracted from the first output signal to produce a resulting signal (block 120 in FIG. 8). The image representing the resulting signal in this example is illustrated in FIG. 11 as resulting image 148. Thus, in this example, background subtraction involves two images 130, 146 to provide a frame pair where the two images 130, 146 are subtracted from each other, whereby specular reflection from the tear film 136 is retained, and while diffuse reflections from the iris and other areas are removed in whole or part.

As illustrated in FIG. 11, the resulting image 148 contains an image of the isolated interference 150 of the specularly reflected light from the tear film 136 with the background signal eliminated or reduced (block 122 in FIG. 8). In this manner, the resulting signal (representing the resulting image 148 in FIG. 11) includes an interference signal having signal improved purity and contrast in the area or region of interest 134 on the tear film 136. As will be discussed later in this application, the resulting signal provides for accurate analysis of interference interactions from the interference signal of specular reflections from the tear film 136 to in turn accurately measure TFLT. Any method or device to obtain the first and second images of the tear film 136 and perform the subtraction of background signal in the second image 146 from the first image 130 may be employed. Other specific examples are discussed throughout the remainder of this application.

An optional registration function may be performed between the first image(s) 130 and the second image(s) 146 before subtraction is performed to ensure that an area or point in the second image(s) 146 to be subtracted from the first image(s) 130 is for an equivalent or corresponding area or point on the first image(s) 130. For example, a set of homologous points may be taken from the first and second images 130, 146 to calculate a rigid transformation matrix between the two images. The transformation matrix allows one point on one image (e.g., x1, y1) to be transformed to an equivalent two-dimensional (2D) image on the other image (e.g., x2, y2). For example, the Matlab® function “cp2tform” can be employed in this regard. Once the transformation matrix is determined, the transformation matrix can be applied to every point in the first and second images, and then each re-interpolated at the original points. For example, the Matlab® function “imtransform” can be employed in this regard. This allows a point from the second image (e.g., x2, y2) to be subtracted from the correct, equivalent point (e.g., x1, y1) on the first image(s) 130, in the event there is any movement in orientation or the patient's eye between the capture of the first and second images 130, 146. The first and second images 130, 146 should be captured close in time. A similar registration technique is explained in greater detail later on in this disclosure.

Note that while this example discusses a first image and a second image captured by the imaging device 80 and a resulting first output signal and second output signal, the first image and the second image may comprise a plurality of images taken in a time-sequenced fashion. If the imaging device 80 is a video camera, the first and second images may contain a number of sequentially-timed frames governed by the frame rate of the imaging device 80. The imaging device 80 produces a series of first output signals and second output signals. If more than one image is captured, the subtraction performed in a first image should ideally be from a second image taken immediately after the first image so that the same or substantially the same lighting conditions exist between the images so the background signal in the second image is present in the first image.

The subtraction of the second output signal from the first output signal can be performed in real time. Alternatively, the first and second output signals can be recorded and processed at a later time. The illuminator 76 may be controlled to oscillate off and on quickly so that first and second images can be taken and the second output signal subtraction from the first output signal be performed in less than one second. For example, if the illuminator 76 oscillates between on and off at 30 Hz, the imaging device 80 can be synchronized to capture images of the tear film 92 at 106 frames per second (fps). In this regard, thirty (30) first images and thirty (30) second images can be obtained in one second, with each pair of first and second images taken sequentially.

After the interference of the specularly reflected light is captured and a resulting signal containing the interference signal is produced and processed, the interference signal or representations thereof can be compared against a tear film layer interference model to measure TFLT. The interference signal can be processed and converted by the imaging device into digital red-green-blue (RGB) component values which can be compared to RGB component values in a tear film interference model to measure tear film TFLT. The tear film interference model is based on modeling the lipid layer of the tear film in various LLTs and representing resulting interference interactions in the interference signal of specularly reflected light from the tear film model when illuminated by the light source. The tear film interference model can be a theoretical tear film interference model where the particular light source, the particular imaging device, and the tear film layers are modeled mathematically, and the resulting interference signals for the various LLTs recorded when the modeled light source illuminates the modeled tear film layers recorded using the modeled imaging device. The settings for the mathematically modeled light source and imaging device should be replicated in the illuminator 76 and imaging device 80 used in the OSI device 70. Alternatively, the tear film interference model can be based on a phantom tear film model, comprised of physical phantom tear film layers wherein the actual light source is used to illuminate the phantom tear film model and interference interactions in the interference signal representing interference of specularly reflected light are empirically observed and recorded using the actual imaging device.

The aqueous layer may be modeled in the tear film interference model to be of an infinite, minimum, or varying thickness. If the aqueous layer is modeled to be of an infinite thickness, the tear film interference model assumes no specular reflections occur from the aqueous-to-mucin layer transition 108 (see FIG. 7). If the aqueous layer 106 is modeled to be of a certain minimum thickness (e.g., ≧2 μm), the specular reflection from the aqueous-to-mucin layer transition 108 may be considered negligible on the effect of the convolved RGB signals produced by the interference signal. In either case, the tear film interference model will only assume and include specular reflections from the lipid-to-aqueous layer transition 102. Thus, these tear film interference model embodiments allow measurement of LLT regardless of ALT. The interference interactions in the interference signal are compared to the interference interactions in the tear film interference model to measure LLT.

Alternatively, if the aqueous layer 106 is modeled to be of varying thicknesses, the tear film interference model additionally includes specular reflections from the aqueous-to-mucin layer transition 108 in the interference interactions. As a result, the tear film interference model will include two-dimensions of data comprised of interference interactions corresponding to various LLT and ALT combinations. The interference interactions from the interference signal can be compared to interference interactions in the tear film interference model to measure both LLT and ALT. More information regarding specific tear film interference models will be described later in this application.

In the above described embodiment in FIGS. 8-11, the second image 146 of the tear film 136 contains a background signal. Only ambient light illuminates the tear film 136 and eye 132 structures beneath. Thus, the second image 146 and the resulting second output signal produced by the imaging device 80 from the second image 146 does not include background signal resulting from scattered light from the patient's face and eye structures as a result of diffuse illumination by the illuminator 76. Only scattered light resulting from ambient light is included in the second image 146. However, scattered light resulting from diffuse illumination by the illuminator 76 is included in background signal in the first image 130 containing the interference interactions of specularly reflected light from the tear film 136.

Further, because the first image 130 is captured when the illuminator 76 is illuminating the tear film, the intensity of the eye structures beneath the tear film 136 captured in the first image 130, including the iris, are brighter than captured in the second image 146. Thus, in other embodiments described herein, the imaging device 80 is controlled to capture a second image of the tear film 136 when obliquely illuminated by the illuminator 76. As a result, the captured second image additionally includes background signal from scattered light as a result of diffuse illumination by the illuminator 76 as well as a higher intensity signal of the eye directly illuminated structures beneath the tear film 136. Thus, when the second output signal is subtracted from the first output signal, the higher intensity eye structure background and the component of background signal representing scattered light as a result of diffuse illumination by the illuminator 76, as well as ambient and stray light, are subtracted or substantially subtracted from the resulting signal thereby further increasing the interference signal purity and contrast in the resulting signal. The resulting signal can then be processed and analyzed to measure TFLT, as will be described in detail later in this application.

Exemplary OSI Devices

The above discussed illustrations provide examples of illuminating and imaging a patient's TFLT. These principles are described in more detail with respect to a specific example of an OSI device 170 illustrated in FIGS. 12-55F and described below throughout the remainder of this application. The OSI device 170 can illuminate a patient's tear film, capture interference information from the patient's tear film, and process and analyze the interference information to measure TFLT. Further, the OSI device 170 includes a number of optional pre-processing features that may be employed to process the interference signal in the resulting signal to enhance TFLT measurement. The OSI device 170 may include a display and user interface to allow a physician or technician to control the OSI device 170 to image a patient's eye and tear film and measure the patient's TFLT.

Illumination and Imaging

In this regard, FIG. 12 illustrates a perspective view of the OSI device 170. The OSI device 170 is designed to facilitate imaging of the patient's ocular tear film and processing and analyzing the images to determine characteristics regarding a patient's tear film. The OSI device 170 includes an imaging device and light source in this regard, as will be described in more detail below. As illustrated in FIG. 12, the OSI device 170 is comprised generally of a housing 172, a display monitor (“display”) 174, and a patient head support 176. The housing 172 may be designed for table top placement. The housing 172 rests on a base 178 in a fixed relationship. As will be discussed in more detail below, the housing 172 houses an imaging device and other electronics, hardware, and software to allow a clinician to image a patient's ocular tear film. A light source 173 (also referred to herein as “illuminator 173”) is also provided in the housing 172 and provided behind a diffusing translucent window 175. The translucent window 175 may be a flexible, white, translucent acrylic plastic sheet.

To image a patient's ocular tear film, the patient places his or her head in the patient head support 176 and rests his or her chin on a chin rest 180. The chin rest 180 can be adjusted to align the patient's eye and tear film with the imaging device inside the housing 172, as will be discussed in more detail below. The chin rest 180 may be designed to support up to two (2) pounds of weight, but such is not a limiting factor. A transparent window 177 allows the imaging device inside the housing 172 to have a clear line of sight to a patient's eye and tear film when the patient's head is placed in the patient head support 176. The first polarizer 52(1) shown in dashed line is behind the transparent window 177 and within the imaging path of the imaging device (not visible). The second polarizer 56(1) is also shown in dashed line. However, in this example the second polarizer 56(1) is shown translated away from the imaging path of the imaging device. The OSI device 170 is designed to image one eye at a time, but can be configured to image both eyes of a patient, if desired.

In general, the display 174 provides input and output from the OSI device 170. For example, a user interface can be provided on the display 174 for the clinician to operate the OSI device 170 and to interact with a control system provided in the housing 172 that controls the operation of the OSI device 170, including an imaging device, an imaging device positioning system, a light source, other supporting hardware and software, and other components. For example, the user interface can allow control of imaging positioning, focus of the imaging device, and other settings of the imaging device for capturing images of a patient's ocular tear film. The control system may include a general purpose microprocessor or computer with memory for storage of data, including images of the patient's eye and tear film. The microprocessor should be selected to provide sufficient processing speed to process images of the patient's tear film and generate output characteristic information about the tear film (e.g., one minute per twenty second image acquisition). The control system may control synchronization of activation of the light source and the imaging device to capture images of areas of interest on the patient's ocular tear film when properly illuminated. Various input and output ports and other devices can be provided, including but not limited to a joystick for control of the imaging device, USB ports, wired and wireless communication including Ethernet communication, a keyboard, a mouse, speaker(s), etc. A power supply is provided inside the housing 172 to provide power to the components therein requiring power. A cooling system, such as a fan, may also be provided to cool the OSI device 170 from heat generating components therein.

The display 174 is driven by the control system to provide information regarding a patient's imaged tear film, including TFLT. The display 174 also provides a graphical user interface (GUI) to allow a clinician or other user to control the OSI device 170. To allow for human diagnosis of the patient's tear film, images of the patient's ocular tear film taken by the imaging device in the housing 172 can also be displayed on the display 174 for review by a clinician, as will be illustrated and described in more detail below. The images displayed on the display 174 may be real-time images being taken by the imaging device, or may be previously recorded images stored in memory. To allow for different orientations of the OSI device 170 to provide a universal configuration for manufacturing, the display 174 can be rotated about the base 178. The display 174 is attached to a monitor arm 182 that is rotatable about the base 178, as illustrated. The display 174 can be placed opposite of the patient head support 176, as illustrated in FIG. 12, if the clinician desires to sit directly across from the patient. Alternatively, display 174 can be rotated either left or right about the X-axis to be placed adjacent to the patient head support 176. The display 174 may be a touch screen monitor to allow a clinician or other user to provide input and control to the control system inside the housing 172 directly via touch of the display 174 for control of the OSI device 170. The display 174 illustrated in FIG. 12 is a fifteen inch (15″) flat panel liquid crystal display (LCD). However, the display 174 may be provided of any type or size, including but not limited to a cathode ray tube (CRT), plasma, LED, OLED, projection system, etc.

FIG. 13 illustrates a side view of the OSI device 170 of FIG. 12 to further illustrate imaging of a patient's eye and ocular tear film. As illustrated therein, a patient places their head 184 in the patient head support 176. More particularly, the patient places their forehead 186 against a headrest 188 provided as part of the patient head support 176. The patient places their chin 190 in the chin rest 180. The patient head support 176 is designed to facilitate alignment of a patient's eye 192 with the OSI device 170, and in particular, an imaging device 194 (and illuminator) shown as being provided inside the housing 172. The chin rest 180 can be adjusted higher or lower to move the patient's eye 192 with respect to the OSI device 170. The first polarizer 52(1) shown in dashed line is within the imaging path of the imaging device 194. The second polarizer 56(1) is also shown in dashed line. However, in this example the second polarizer 56(1) is shown translated below the first polarizer 52(1) and away from the imaging path of the imaging device.

OSI Device Employing Rotatable Polarizer

As shown in FIGS. 14A and 14B, the imaging device 194 can be used to image the patient's ocular tear film to determine characteristics of the patient's tear film. In particular, the imaging device 194 is used to capture interference interactions of the specularly reflected light from the patient's tear film when illuminated by the light source 196 (also referred to herein as “illuminator 196”) as well as background signal. In the OSI device 170, the imaging device 194 is the “The Imaging Source” model DFK21BU04 charge coupling device (CCD) digital video camera 198, but many types of metrological grade cameras or imaging devices can be provided. A CCD camera enjoys characteristics of efficient light gathering, linear behavior, cooled operation, and immediate image availability. A linear imaging device is one that provides an output signal representing a captured image which is precisely proportional to the input signal from the captured image. Thus, use of a linear imaging device (e.g., gamma correction set to 1.0, or no gamma correction) provides undistorted interference data which can then be analyzed using linear analysis models. In this manner, the resulting images of the tear film do not have to be linearized before analysis, thus saving processing time. Gamma correction can then be added to the captured linear images for human-perceptible display on the non-linear display 174 in the OSI device 170 (FIGS. 12 and 13). Alternatively, the opposite scenario could be employed. That is, a non-linear imaging device or non-linear setting would be provided to capture tear film images, wherein the non-linear data representing the interference interactions of the interference signal can be provided to a non-linear display monitor without manipulation to display the tear film images to a clinician. The non-linear data would be linearized for tear film processing and analysis to estimate tear film layer thickness.

The video camera 198 is capable of producing lossless full motion video images of the patient's eye. As illustrated in FIGS. 14A and 14B, the video camera 198 has a depth of field defined by the angle between rays 199 and the lens focal length that allows the patient's entire tear film to be in focus simultaneously. The video camera 198 has an external trigger support so that the video camera 198 can be controlled by a control system to image the patient's eye. The video camera 198 includes a lens and a rotatable polarizer 208 that can fit within the housing 172 (FIG. 13) that is usable in place of both the first and second polarizers 52(1) and 56(1).

Employing the rotatable polarizer 208 is less mechanically complex than alternating the first and second polarizers 52(1) and 56(1) into the imaging path of the video camera 198. For example, the rotatable polarizer 208 is always in the imaging path of the video camera 198. Therefore, the rotatable polarizer 208 only needs to be rotated from one polarization orientation to another between a first and second image capture. Moreover, due to its relatively low mechanical complexity, the rotatable polarizer 208 can offer a relatively fast response when rotating from one polarization orientation to another. This relatively fast response allows the rotatable polarizer 208 to be more easily synchronized with the video camera 198.

The rotatable polarizer 208 is disposed in an imaging path of the imaging device 194, which in this case is the video camera 198. The rotatable polarizer 208 has a center axis shown in dashed line extending to the eye 192. The rotatable polarizer 208 is selectively rotatable about the center axis to provide a first polarization axis relative to the polarization plane of the specularly reflected light from the ROI of the ocular tear film on the eye 192 during a capture of at least one first image. The rotatable polarizer 208 is also selectively rotatable to provide a second polarization axis that is perpendicular or substantially perpendicular relative to the first polarization axis during the capture of at least one second image. An actuator such as a motor could be coupled to the rotatable polarizer 208 to rotate the from one polarization orientation to another in synchronization with the video camera 198.

The video camera 198 in this embodiment has a resolution of 640×480 pixels and is capable of frame rates up to sixty (60) frames per second (fps). The lens system employed in the video camera 198 images a 16×12 mm dimension in a sample plane onto an active area of a CCD detector within the video camera 198. As an example, the video camera 198 may be the DBK21AU04 Bayer VGA (640×480) video camera using a Pentax VS-LD25 Daitron 25-mm fixed focal length lens. Other camera models with alternate pixel size and number, alternate lenses, (etc) may also be employed.

Although a video camera 198 is provided in the OSI device 170, a still camera could also be used if the frame rate is sufficiently fast enough to produce high quality images of the patient's eye. High frame rate in frames per second (fps) facilitate high quality subtraction of background signal from a captured interference signal representing specularly reflected light from a patient's tear film, and may provide less temporal (i.e., motion) artifacts (e.g., motion blurring) in captured images, resulting in high quality captured images. This is especially the case since the patient's eye may move irregularly as well as blinking, obscuring the tear film from the imaging device during examination.

A camera positioning system 200 is also provided in the housing 172 of the OSI device 170 to position the video camera 198 for imaging of the patient's tear film. The camera positioning system 200 is under the control of a control system. In this manner, a clinician can manipulate the position of the video camera 198 to prepare the OSI device 170 to image the patient's tear film. The camera positioning system 200 allows a clinician and/or control system to move the video camera 198 between different patients' eyes 192, but can also be designed to limit the range of motion within designed tolerances. The camera positioning system 200 also allows for fine tuning of the video camera 198 position. The camera positioning system 200 includes a stand 202 attached to a base 204. A linear servo or actuator 206 is provided in the camera positioning system 200 and connected between the stand 202 and a camera platform 207 supporting the video camera 198 to allow the video camera 198 to be moved in the vertical (i.e., Y-axis) direction.

In this embodiment of the OSI device 170, the camera positioning system 200 may not allow the video camera 198 to be moved in the X-axis or the Z-axis (in and out of FIG. 14A), but other embodiments of the disclosure are not so limited. The illuminator 196 is also attached to the camera platform 207 such that the illuminator 196 maintains a fixed geometric relationship to the video camera 198. Thus, when the video camera 198 is adjusted to the patient's eye 192, the illuminator 196 is automatically adjusted to the patient's eye 192 in the same regard as well. This may be important to enforce a desired distance (d) and angle of illumination (Φ) of the patient's eye 192, as illustrated in FIG. 14A, to properly capture the interference interactions of the specularly reflected light from the patient's tear film at the proper angle of incidence according to Snell's law, since the OSI device 170 is programmed to assume a certain distance and certain angles of incidence. In the OSI device 170 in FIG. 14A, the angle of illumination (Φ) of the patient's eye 192 relative to the video camera 198 axis is approximately 30 degrees at the center of the illuminator 196 and includes a relatively large range of angles from about 5 to 60 degrees, but any angle may be provided.

FIG. 15 is a flowchart of an exemplary process for OSI device 170 that incorporates the rotatable polarizer 208 for obtaining one or more interference signals from images of a tear film representing specularly reflected light from the tear film with background signal subtracted or substantially subtracted. Against the backdrop of the OSI device 170 in FIGS. 14A and 14B, FIG. 15 illustrates a flowchart discussing how the OSI device 170 can be used to obtain interference interactions of specularly reflected light from the tear film 92, which can be used to measure TFLT. Interference interactions of specularly reflected light from the tear film 92 are first obtained and discussed before measurement of TFLT is discussed. In this embodiment as illustrated in FIG. 15, the process starts by adjusting the patient 184 with regard to the illuminator 196 and the imaging device 194 (block 210). The illuminator 196 is then controlled to illuminate the patient's 184 tear film 92 (block 212).

Next, the imaging device 194 is controlled to be focused on the anterior surface 98 of the lipid layer 96 such that the interference interactions of specularly reflected light from the tear film 92 are captured in first image(s) (block 214). An example of the first image(s) captured by the imaging device is provided in FIG. 9. As illustrated therein, a first image 130 of a patient's eye 192 is shown that has been illuminated with the illuminator 196. The illuminator 196 and the imaging device 194 may be controlled to illuminate an area or region of interest 134 on a tear film 136 that does not include a pupil 138 of the eye 132 so as to reduce reflex tearing. Reflex tearing will temporarily lead to thicker aqueous and lipid layers, thus temporarily altering the interference signals of specularly reflected light from the tear film 136. As shown in FIG. 9, when the imaging device 194 is focused on an anterior surface 142 of the lipid layer 144 of the tear film 136, interference interactions 140 of the interference signal of the specularly reflected light from the tear film 136 as a result of illumination by the illuminator 76 are captured in the area or region of interest 134 in the first image 130.

The interference interactions 140 appear to a human observer as colored patterns as a result of the wavelengths present in the interference of the specularly reflected light from the tear film 136.

However, even though the background signal is reduced by the rotatable polarizer 208, a portion of the background signal is also captured in the first image 130. The background signal is added to the specularly reflected light in the area or region of interest 134 and included outside the area or region of interest 134 as well. Background signal is light that is not specularly reflected from the tear film 136 and thus contains no interference information. Background signal can include stray and ambient light entering into the imaging device 194, scattered light from the patient's 184 face, eyelids, and/or eye 192 structures outside and beneath the tear film 136 as a result of stray light, ambient light and diffuse illumination by the illuminator 196, and images of structures beneath the tear film 136. For example, the first image 130 includes the iris of the eye 132 beneath the tear film 136. Background signal adds a bias (i.e., offset) error to the captured interference of specularly reflected light from the tear film 136 thereby reducing its signal strength and contrast. Further, if the background signal has a color hue different from the light of the light source, a color shift can also occur due to the interference of specularly reflected light from the tear film 136 in the first image 130.

The imaging device 194 produces a first output signal that represents the light rays captured in the first image 130. Because the first image 130 contains light rays from specularly reflected light as well as the background signal, the first output signal produced by the imaging device 194 from the first image 130 will contain an interference signal representing the captured interference of the specularly reflected light from the tear film 136 with a bias (i.e., offset) error caused by the background signal. As a result, the first output signal analyzed to measure TFLT may contain error as a result of the background signal bias (i.e., offset) error.

Thus, in this embodiment, the first output signal generated by the imaging device 194 as a result of the first image 130 is processed to subtract or substantially subtract the background signal from the interference signal to reduce error before being analyzed to measure TFLT. This is also referred to as “background subtraction.” Background subtraction is the process of removing unwanted reflections from images. In this regard, the imaging device 194 is controlled to capture a second image 146 of the tear film 136. However, before the second image 146 is captured, the rotatable polarizer 208 is rotated from a first orientation that reduces background signal to a second orientation that reduces specularly reflected light (block 216 in FIG. 15). In this way, the second image 146 will contain mostly background signal and when the second image 146 is subtracted from the first image 130 the captured interference of specularly reflected light from the tear film 136 will not be reduced or at least not significantly reduced.

The second image 146 should be captured using the same imaging device 194 settings and focal point as when capturing the first image 130 so that the first image 130 and second image 146 form corresponding image pairs captured within a short time of each other. The imaging device 194 produces a second output signal containing background signal present in the first image 130 (block 218 in FIG. 15). To eliminate or reduce this background signal from the first output signal, the second output signal is subtracted from the first output signal to produce a resulting signal (block 220 in FIG. 15). The image(s) representing the resulting signal(s) containing interference signal(s) of specularly reflected light from the tear film is produced (block 222 in FIG. 15). In this example the resulting image 148 is illustrated in FIG. 11. Thus, in this example, background subtraction involves two images 130, 146 to provide a frame pair where the two images 130, 146 are subtracted from each other, whereby specular reflection from the tear film 136 is retained, and while diffuse reflections from the iris and other areas are removed in whole or part.

Illuminator Details

FIGS. 16-18 provide more detail on the illuminator 196. As illustrated in FIG. 16, the exemplary illuminator 196 is provided on an arced surface 230 (see also, FIGS. 17-18) of approximately 75 degrees to provide a large area, broad spectrum light source covering the visible regions of approximately 400 nanometers (nm) to 700 nm. In this embodiment, the arced surface 230 has a radius to an imaginary center of approximately 190 mm (“r” in FIG. 16) and has a face 250 mm high by 100 mm wide. The arced surface 230 could be provided as a flat surface, but an arced surface may allow for: better illumination uniformity, and, a smaller sized illuminator 196 for packaging constraints, while providing the same effective illumination area capability. In this example, the illuminator 196 is a Lambertian emitter wherein the light emitter has approximately the same intensity in all directions; however, other embodiments of the present disclosure are not so limited. The illuminator 196 is arranged so that, from the perspective of the video camera 198, emitted light rays are specularly reflected from the tear film of the patient's eye 192 and undergo constructive and destructive interference in the lipid layer and layers beneath the lipid layer. In this embodiment, the illuminator 196 is comprised of high efficiency, white light emitting diodes (LEDs) 232 (see FIGS. 17 and 18) mounted on a printed circuit board (PCB) 236 (FIG. 17). Supporting circuitry (not shown) may be included to control operation of the LEDs 232, and to automatically shut off the LEDs 232 when the OSI device 170 is not in use. Each LED 232 has a 120 degree (“Lambertian”) forward projection angle, a 1350 mcd maximum intensity, manufactured by LEDtronics. Other light sources other than LEDs are also possible, including but not limited to lasers, incandescent light, and organic LEDs (OLEDs), as examples. Further, the light source is not required to be a Lambertian emitter. For example, the light emitted from the light source may be collimated.

As illustrated in FIG. 18, the PCB 236 is placed inside an illuminator housing 242. The illuminator housing 242 is comprised of two side panels 244A, 244B that are disposed on opposite sides of the arced surfaced 230 when held by base panel 246 and top panel 248, and also includes a rear panel 234. The arced surface 230 is comprised of a diffuser 240 to diffuse the light emitted by the LEDs 232. The diffuser 240 can be selected to minimize intensity reduction, while providing sufficient scattering to make the illumination uniform light wave fall off on the light emitted by the outside LEDs 232. The diffuser 240, PCB 236, and rear panel 234 are flexible and fit within grooves 250 located in the top panel 248 and base panel 246, and grooves 252 located in the side panels 244A, 244B. The illuminator housing 242 is snapped together and the side panels 244A, 244B are then screwed to the top panel 248 and base panel 246.

The diffuser 240 may also be comprised of more than one diffuser panel to improve uniformity in the light emitted from the illuminator 196. The side panels 244A, 244B and the base panel 246 and top panel 248 form baffles around the PCB 236 and the LEDs 232. The inside of these surfaces may contain a reflective film (e.g., 3M ESR film) to assist in the uniformity of light emitted by the LEDs 232. The reflective film may assist in providing a uniform light intensity over an entire area or region of interest on a patient's tear film. This may be particularly an issue on the outer edges of the illumination pattern. The diffuser 240 should also be sufficiently tightly held to the edges in the illuminator housing 242 to prevent or reduce shadows on in the illumination pattern.

OSI Device Employing Polarizer Wheel

FIG. 19A is a side view of the imaging device 194 and illuminator 196 configured with a polarizer wheel 260 having a plurality of polarizers. FIG. 19B is a top view of the imaging device 194 and illuminator 196 with the polarizer wheel 260. In particular, the polarizer wheel 260 includes a plurality of polarizers made up of a first polarizer 52(2) and a second polarizer 56(2). The polarizer wheel 260 is selectively rotatable such that the first polarizer 52(2) is disposed in an imaging path of the imaging device 194 during the capture of the at least one first image, and wherein the second polarizer 56(2) is alternately disposed in the imaging path of the imaging device 194 during the capture of the at least one second image. In this manner, the first polarizer 52(2) and the second polarizer 56(2) are alternately rotatable into the imaging path of the imaging device 194 that includes rays 199 and is centered on the dashed line that extends from eye 192. A motor 262 coupled to polarizer wheel 260 is controllable to selectively synchronize the rotation of the polarizer wheel 260 with the image capturing by the imaging device 194.

The first polarizer 52(2) has a polarization axis 54(2) that is parallel or substantially parallel to the polarization plane of the specularly reflected light from the ROI of the ocular tear film 92 (FIG. 7) to pass or substantially pass the specularly reflected light to the imaging device 194 while reducing the background signal. Furthermore, the second polarizer 56(2) has a polarization axis 58(2) that is perpendicular or substantially perpendicular to the polarization plane of the specularly reflected light from the ROI of the ocular tear film 92 (FIG. 7) to eliminate or substantially eliminate the specularly reflected light while passing a portion of background signal to the imaging device 194.

FIG. 20 is a flowchart of an exemplary process for the OSI device 170 that incorporates the polarizer wheel 260 for obtaining one or more interference signals from images of a tear film 92 representing specularly reflected light from the tear film 92 with background signal subtracted or substantially subtracted. Against the backdrop of the OSI device 170 in FIGS. 19A and 19B, FIG. 20 illustrates a flowchart discussing how the OSI device 170 can be used to obtain interference interactions of specularly reflected light from the tear film 92, which can be used to measure TFLT. Interference interactions of specularly reflected light from the tear film 92 are first obtained and discussed before measurement of TFLT is discussed. In this embodiment as illustrated in FIG. 20, the process starts by adjusting the patient 184 with regard to the illuminator 196 and the imaging device 194 (block 270). The illuminator 196 is controlled to illuminate the patient's 184 tear film 92. The imaging device 194 is controlled to be focused on the anterior surface 98 of the lipid layer 96 such that the interference interactions of specularly reflected light from the tear film 92 are collected and are observable. Thereafter, the patient's 184 tear film 92 is illuminated by the illuminator 196 (block 272).

The imaging device 194 is then controlled and focused on the lipid layer 96 to collect specularly reflected light from an area or ROI 134 on a tear film 92 as a result of illuminating the tear film 92 with the illuminator 196 in a first image (block 274, FIG. 20). An example of the first image by the illuminator 196 is provided in FIG. 9. As illustrated therein, a first image 130 of a patient's eye 132 is shown that has been illuminated with the illuminator 196. The illuminator 196 and the imaging device 194 may be controlled to illuminate an area or ROI 134 on a tear film 136 that does not include a pupil 138 of the eye 132 so as to reduce reflex tearing. Reflex tearing will temporarily lead to thicker aqueous and lipid layers, thus temporarily altering the interference signals of specularly reflected light from the tear film 136. As shown in FIG. 9, when the imaging device 194 is focused on an anterior surface 142 of the lipid layer 144 of the tear film 136, interference interactions 140 of the interference signal of the specularly reflected light from the tear film 136 as a result of illumination by the illuminator 196 are captured in the area or ROI 134 in the first image 130. The interference interactions 140 appear to a human observer as colored patterns as a result of the wavelengths present in the interference of the specularly reflected light from the tear film 136.

However, even though the background signal is reduced by the first polarizer 52(2), a portion of the background signal is also captured in the first image 130. The background signal is added to the specularly reflected light in the area or ROI 134 and included outside the area or ROI 134 as well. Background signal is light that is not specularly reflected from the tear film 136 and thus contains no interference information. Background signal can include stray and ambient light entering into the imaging device 194, scattered light from the patient's 184 face, eyelids, and/or eye 132 structures outside and beneath the tear film 136 as a result of stray light, ambient light and diffuse illumination by the illuminator 196, and images of structures beneath the tear film 136. For example, the first image 130 includes the iris of the eye 132 beneath the tear film 136. Background signal adds a bias (i.e., offset) error to the captured interference of specularly reflected light from the tear film 136 thereby reducing its signal strength and contrast. Further, if the background signal has a color hue different from the light of the light source, a color shift can also occur due to the interference of specularly reflected light from the tear film 136 in the first image 130. The imaging device 194 produces a first output signal that represents the light rays captured in the first image 130. Because the first image 130 contains light rays from specularly reflected light as well as the background signal, the first output signal produced by the imaging device 194 from the first image 130 will contain an interference signal representing the captured interference of the specularly reflected light from the tear film 136 with a bias (i.e., offset) error caused by the background signal. As a result, the first output signal analyzed to measure TFLT may contain error as a result of the background signal bias (i.e., offset) error.

Thus, in this embodiment, the first output signal generated by the imaging device 194 as a result of the first image 130 is processed to subtract or substantially subtract the background signal from the interference signal to reduce error before being analyzed to measure TFLT. This is also referred to as “background subtraction.” Background subtraction is the process of removing unwanted reflections from images. In this regard, the imaging device 194 is controlled to capture a second image 146 of the tear film 136. However, before the second image 146 is captured, the polarizer wheel 260 is rotated such that the second polarizer 56(2) is disposed in the imaging path of the imaging device 194 in a second orientation that is polarized 90° relative to the first polarization orientation (block 276 in FIG. 20). In this way, the second image 146 will contain mostly background signal and when the second image 146 is subtracted from the first image 130 the captured interference of specularly reflected light from the tear film 136 will not be reduced or at least not significantly reduced.

The second image 146 should be captured using the same imaging device 194 settings and focal point as when capturing the first image 130 so that the first image 130 and second image 146 form corresponding image pairs captured within a short time of each other. The imaging device 194 produces a second output signal containing background signal present in the first image 130 (block 278 in FIG. 20). To eliminate or reduce this background signal from the first output signal, the second output signal is subtracted from the first output signal to produce a resulting signal (block 280 in FIG. 20). The image representing the resulting signal in this example is illustrated in FIG. 11 as resulting image 148 (block 282 in FIG. 20). Thus, in this example, background subtraction involves two images 130, 146 to provide a frame pair where the two images 130, 146 are subtracted from each other, whereby specular reflection from the tear film 136 is retained, and while diffuse reflections from the iris and other areas are removed in whole or part.

OSI Device Employing Two Imaging Devices/Non-Polarizing Beam Splitter

FIG. 21A is a side view and FIG. 21B is a top view of the OSI device 170 with a dual imaging device configuration. The first imaging device 194 is configured to capture the at least one first image, and a second imaging device 194(2) is configured to capture the at least one second image. A non-polarizing beam splitter 286 is configured to direct a first portion of the specularly reflected light including the background signal to the first imaging device 194 while simultaneously directing a second portion of the specularly reflected light including the background signal to the second imaging device 194(2).

A first polarizer 52(3) is disposed in an imaging path of the first imaging device 194. The first polarizer 52(3) has a polarization axis that is parallel or substantially parallel to the polarization plane of the specularly reflected light from the ROI 134 of the ocular tear film to pass or substantially pass the specularly reflected light to the first imaging device 194 while reducing the background signal. A second polarizer 56(3) is disposed in an imaging path of a second imaging device 194(2). The second polarizer 56(3) has a polarization axis that is perpendicular or substantially perpendicular to the polarization plane of the specularly reflected light from the ROI 134 of the ocular tear film 92 to reduce or eliminate the specularly reflected light while passing a portion of background signal to the second imaging device 194(2). In this exemplary case, the second imaging device 194(2) is a video camera 198(1), which is the same type and model as the video camera 198.

FIG. 22 is a flowchart of an exemplary process for the dual camera configuration of FIGS. 21A-21B, FIGS. 23A-23B, and FIGS. 24A-24B for obtaining one or more interference signals from images of a tear film 92 representing specularly reflected light from the tear film 92 with background signal subtracted or substantially subtracted. Against the backdrop of the OSI device 170 in FIGS. 21A-21B, FIGS. 23A-23B, and FIGS. 24A-24B, FIG. 22 illustrates a flowchart discussing how the OSI device 170 can be used to obtain interference interactions of specularly reflected light from the tear film 92, which can be used to measure TFLT. Interference interactions of specularly reflected light from the tear film 92 are first obtained and discussed before measurement of TFLT is discussed. In this embodiment as illustrated in FIG. 22, the process starts by adjusting the patient 184 with regard to an illuminator 196 and an imaging device 194 (block 290). The illuminator 196 is controlled to illuminate the patient's 184 tear film 92. The imaging device 194 is controlled to be focused on the anterior surface 98 of the lipid layer 96 such that the interference interactions of specularly reflected light from the tear film 92 are collected and are observable. Thereafter, the patient's 184 tear film 92 is illuminated by the illuminator 196 (block 292).

The imaging device 194 is then controlled and focused on the lipid layer 96 to collect specularly reflected light from an area or ROI 134 on a tear film 92 as a result of illuminating the tear film 92 with the illuminator 196 in a first image (block 294, FIG. 22). An example of the first image by the illuminator 196 is provided in FIG. 9. As illustrated therein, a first image 130 of a patient's eye 132 is shown that has been illuminated with the illuminator 196. The illuminator 196 and the imaging device 194 may be controlled to illuminate an area or ROI 134 on a tear film 136 that does not include a pupil 138 of the eye 132 so as to reduce reflex tearing. Reflex tearing will temporarily lead to thicker aqueous and lipid layers, thus temporarily altering the interference signals of specularly reflected light from the tear film 136. As shown in FIG. 9, when the imaging device 194 is focused on an anterior surface 142 of the lipid layer 144 of the tear film 136, interference interactions 140 of the interference signal of the specularly reflected light from the tear film 136 as a result of illumination by the illuminator 196 are captured in the area or ROI 134 in the first image 130. The interference interactions 140 appear to a human observer as colored patterns as a result of the wavelengths present in the interference of the specularly reflected light from the tear film 136.

However, even though the background signal is reduced by the first polarizer 52(3), a portion of the background signal is also captured in the first image 130. The background signal is added to the specularly reflected light in the area or ROI 134 and included outside the area or ROI 134 as well. Background signal is light that is not specularly reflected from the tear film 136 and thus contains no interference information. Background signal can include stray and ambient light entering into the imaging device 194, scattered light from the patient's 184 face, eyelids, and/or eye 132 structures outside and beneath the tear film 136 as a result of stray light, ambient light and diffuse illumination by the illuminator 196, and images of structures beneath the tear film 136. For example, the first image 130 includes the iris of the eye 132 beneath the tear film 136. Background signal adds a bias (i.e., offset) error to the captured interference of specularly reflected light from the tear film 136 thereby reducing its signal strength and contrast. Further, if the background signal has a color hue different from the light of the light source, a color shift can also occur due to the interference of specularly reflected light from the tear film 136 in the first image 130. The imaging device 194 produces a first output signal that represents the light rays captured in the first image 130. Because the first image 130 contains light rays from specularly reflected light as well as the background signal, the first output signal produced by the imaging device 194 from the first image 130 will contain an interference signal representing the captured interference of the specularly reflected light from the tear film 136 with a bias (i.e., offset) error caused by the background signal. As a result, the first output signal analyzed to measure TFLT may contain error as a result of the background signal bias (i.e., offset) error.

Thus, in this embodiment, the first output signal generated by the imaging device 194 as a result of the first image 130 is processed to subtract or substantially subtract the background signal from the interference signal to reduce error before being analyzed to measure TFLT. This is also referred to as “background subtraction.” Background subtraction is the process of removing unwanted reflections from images. In this regard, the second imaging device 194(2) is controlled simultaneously with the first imaging device 194 to capture a second image 146 of the tear film 136. In this way, the second image 146 will contain mostly background signal and when the second image 146 is subtracted from the first image 130 the captured interference of specularly reflected light from the tear film 136 will not be reduced or at least not significantly reduced.

The second imaging device 194(2) produces a second output signal containing background signal present in the first image 130 (block 294 in FIG. 22). To eliminate or reduce this background signal from the first output signal, the second output signal is subtracted from the first output signal to produce a resulting signal (block 296 in FIG. 22). The image(s) representing the resulting signal(s) containing interference signal(s) of specularly reflected light from the tear film is produced (block 298 in FIG. 22). In this example the resulting image 148 is illustrated in FIG. 11. Thus, in this example, background subtraction involves two images 130, 146 to provide a frame pair where the two images 130, 146 are subtracted from each other, whereby specular reflection from the tear film 136 is retained, and while diffuse reflections from the iris and other areas are removed in whole or part.

OSI Device Employing Two Imaging Devices/Polarizing Beam Splitter

FIG. 23A is a side view and FIG. 23B is a top view of the OSI device with yet another dual imaging device configuration. In this embodiment, the first polarizer 52(3) and the second polarizer 56(3) of FIGS. 21A and 21B are replaced by a polarizing beam splitter 300. However, the operation of the embodiment is operated as described by the flowchart of FIG. 22.

In this embodiment, specularly reflected light from the tear film 136 passes largely unimpeded through the polarizing beam splitter 300 and onward to the first imaging device 194. A portion of background signal is also transmitted through the polarizing beam splitter 300 to the first imaging device 194. In contrast, specularly reflected light from the tear film 136 is practically blocked from reflecting to the second imaging device 194(1), while a portion of the background signal is directed to the second imaging device 194(1).

OSI Device Employing Illuminator Polarizer

FIG. 24A is a side view and FIG. 24B is a top view of the OSI device of FIG. 23A and FIG. 23B that further includes a polarizer 302. The polarizer 302 is disposed in the illumination path of the illuminator 196 to polarize multi-wavelength light emitted from the illuminator 196 that is illuminating the ROI 134 of the ocular tear film 136. The polarizer 302 helps further isolate by reducing the amount of unpolarized light that makes up the background signal. The polarizer 302 can be either a linear polarizer or a circular polarizer.

System Level

Now that the imaging and illumination functions of the OSI device 170 have been described, FIG. 25A illustrates a system level diagram illustrating more detail regarding the control system and other internal components of the OSI device 170 provided inside the housing 172 according to one embodiment to capture images of a patient's tear film and process those images. As illustrated therein, a control system 340 is provided that provides the overall control of the OSI device 170. The control system 340 may be provided by any microprocessor-based or computer system. The control system 340 illustrated in FIG. 25A is provided in a system-level diagram and does not necessarily imply a specific hardware organization and/or structure. As illustrated therein, the control system 340 contains several systems. A polarization settings system 341 may be provided that accepts input from a clinician user. The polarization settings may include but are not limited to synchronization values that adjust video camera and polarizer synchronization. A camera settings system 342 may be provided that accepts camera settings from a clinician user. Exemplary camera settings 344 are illustrated, but may be any type according to the type and model of camera provided in the OSI device 170 as is well understood by one of ordinary skill in the art.

The camera settings 344 may be provided to (The Imaging Source) camera drivers 346, which may then be loaded into the video camera 198 upon initialization of the OSI device 170 for controlling the settings of the video camera 198. The settings and drivers may be provided to a buffer 348 located inside the video camera 198 to store the settings for controlling a CCD 350 for capturing ocular image information from a lens 352. Ocular images captured by the lens 352 and the CCD 350 are provided to a de-Bayering function 354 which contains an algorithm for post-processing of raw data from the CCD 350 as is well known. The ocular images are then provided to a video acquisition system 356 in the control system 340 and stored in memory, such as random access memory(s) (RAM(s)) 358. The stored ocular images or signal representations can then be provided to a pre-processing system 360 and a post-processing system 362 to manipulate the ocular images to obtain the interference interactions of the specularly reflected light from the tear film and analyze the information to determine characteristics of the tear film. Pre-processing settings 364 and post-processing settings 366 can be provided to the pre-processing system 360 and post-processing system 362, respectively, to control these functions. The pre-processing settings 364 and the post-processing settings 366 will be described in more detail below. The post-processed ocular images and information may also be stored in mass storage, such as disk memory 368, for later retrieval and viewing on the display 174.

The control system 340 may also contain a visualization system 370 that provides the ocular images to the display 174 to be displayed in human-perceptible form on the display 174. Before being displayed, the ocular images may have to be pre-processed in a pre-processing video function 372. For example, if the ocular images are provided by a linear camera, non-linearity (i.e. gamma correction) may have to be added in order for the ocular images to be properly displayed on the display 174. Further, contrast and saturation display settings 374, which may be controlled via the display 174 or a device communicating to the display 174, may be provided by a clinician user to control the visualization of ocular images displayed on the display 174. The display 174 is also adapted to display analysis result information 376 regarding the patient's tear film, as will be described in more detail below. The control system 340 may also contain a user interface system 378 that drives a graphical user interface (GUI) utility 380 on the display 174 to receive user input 382. The user input 382 can include any of the settings for the OSI device 170, including the camera settings 344, the pre-processing settings 364, the post-processing settings 366, the display settings 374, the visualization system 370 enablement, and video acquisition system 356 enablement, labeled 1-6. The GUI utility 380 may only be accessible by authorized personnel and used for calibration or settings that would normally not be changed during normal operation of the OSI device 170 once configured and calibrated.

Overall Process Flow

FIG. 25B illustrates an exemplary overall flow process performed by the OSI device 170 for capturing tear film images from a patent and analysis for TFLT measurement. As illustrated in FIG. 25B, the first video camera 198 and an optional second video camera 198(1) are connected via a USB port(s) 383 to the control system 340 (see FIG. 25A) for control of the first video camera 198 and the second video camera 198(1) and for transferring images of a patient's tear film taken by the video camera 198 back to the control system 340. The control system 340 includes a compatible camera driver 346 to provide a transfer interface between the control system 340 and the video camera 198. Prior to tear film image capture, the configuration or camera settings 344 are loaded into the video camera 198 over the USB port 383 to prepare the video camera 198 for tear film image capture (block 385). Further, an audio video interleaved (AVI) container is created by the control system 340 to store video of tear film images to be captured by the video camera 198 (block 386). At this point, the video camera 198 and control system 340 are ready to capture images of a patient's tear film. The control system 340 waits for a user command to initiate capture of a patient's tear film (blocks 387, 388).

Once image capture is initiated (block 388), the control system enables image capture to the AVI container previously setup (block 386) for storage of images captured by the video camera 198 (block 389). The control system 340 controls the video camera 198 to capture images of the patient's tear film (block 389) until timeout or the user terminates image capture (block 390) and image capture halts or ends (block 391). Images captured by the video camera 198 and provided to the control system 340 over the USB port 383 are stored by the control system 340 in RAM(S) 358.

The captured images of the patient's ocular tear film can subsequently be processed and analyzed to perform TFLT measurement, as described in more detail below and throughout the remainder of this disclosure. The process in this embodiment involves processing tear film image pairs to perform background subtraction, as previously discussed. The processing can include simply displaying the patient's tear film or performing TFLT measurement (block 393). If the display option is selected to allow a technician to visually view the patient's tear film, display processing is performed (block 394) which can be the display processing 370 described in more detail below with regard to FIG. 34. For example, the control system 340 can provide a combination of images of the patient's tear film that show the entire region of interest of the tear film on the display 174. The displayed image may include the background signal or may have the background signal subtracted. If TFLT measurement is desired, the control system 340 performs pre-processing of the tear film images for TFLT measurement (block 395), which can be the pre-processing system 360 described in more detail below with regard to FIG. 26. The control system 340 also performs post-processing of the tear film images for TFLT measurement (block 396), which can be the post-processing system 362 described in more detail below with regard to FIG. 36.

Pre-Processing

FIG. 26 illustrates an exemplary pre-processing system 360 for pre-processing ocular tear film images captured by the OSI device 170 for eventual analysis and TFLT measurement. In this system, the video camera 198 has already taken the first and second images of a patient's ocular tear film, as previously illustrated in FIGS. 9 and 10, and provided the images to the video acquisition system 356. The frames of the first and second images were then loaded into RAM(s) 358 by the video acquisition system 356. Thereafter, as illustrated in FIG. 26, the control system 340 commands the pre-processing system 360 to pre-process the first and second images. An exemplary GUI utility 380 is illustrated in FIG. 27 that may be employed by the control system 340 to allow a clinician to operate the OSI device 170 and control pre-processing settings 364 and post-processing settings 366, which will be described later in this application. In this regard, the pre-processing system 360 loads the first and second image frames of the ocular tear film from RAM(s) 358 (block 400). The exemplary GUI utility 380 in FIG. 27 allows for a stored image file of previously stored video sequence of first and second image frames captured by the video camera 198 by entering a file name in the file name field 451. A browse button 452 also allows searches of the memory for different video files, which can either be buffered by selecting a buffered box 454 or loaded for pre-processing by selecting the load button 456.

If the loaded first and second image frames of the tear film are buffered, they can be played using display selection buttons 458, which will in turn display the images on the display 174. The images can be played on the display 174 in a looping fashion, if desired, by selecting the loop video selection box 460. A show subtracted video selection box 470 in the GUI utility 380 allows a clinician to show the resulting, subtracted video images of the tear film on the display 174 representative of the resulting signal comprised of the second output signal combined or subtracted from the first output signal, or vice versa. Also, by loading the first and second image frames, the previously described subtraction technique can be used to remove background image from the interference signal representing interference of the specularly reflected light from the tear film, as previously described above and illustrated in FIG. 11 as an example. The first image is subtracted from the second image to subtract or remove the background signal in the portions producing specularly reflected light in the second image, and vice versa, and then combined to produce an interference interaction of the specularly reflected light of the entire area or region of interest of the tear film, as previously illustrated in FIG. 11 (block 402 in FIG. 26). For example, this processing could be performed using the Matlab® function “cvAbsDiff.”

The subtracted image containing the specularly reflected light from the tear film can also be overlaid on top of the original image capture of the tear film to display an image of the entire eye and the subtracted image in the display 174 by selecting the show overlaid original video selection box 462 in the GUI utility 380 of FIG. 27. An example of an overlaid original video to the subtracted image of specularly reflected light from the tear film is illustrated in the image 520 of FIG. 28. This overlay is provided so that flashing images of specularly reflected light from the tear film are not displayed, which may be unpleasant to visualize. The image 520 of the tear film illustrated in FIG. 28 was obtained with a DBK 21AU04 Bayer VGA (640×480) video camera having a Pentax VS-LD25 Daitron 25-mm fixed focal length lens with maximum aperture at a working distance of 120 mm and having the following settings, as an example:

Gamma=100 (to provide linearity with exposure value)

Exposure= 1/16 second

Frame rate=60 fps

Data Format=BY8

Video Format=−uncompressed, RGB 24-bit AVI

Hue=180 (neutral, no manipulation)

Saturation=128(neutral, no manipulation)

Brightness=0 (neutral, no manipulation)

Gain=260 (minimum available setting in this camera driver)

White balance=B=78; R=20.

Thresholding

Any number of optional pre-processing steps and functions can next be performed on the resulting combined tear film image(s), which will now be described. For example, an optional threshold pre-processing function may be applied to the resulting image or each image in a video of images of the tear film (e.g., FIG. 11) to eliminate pixels that have a subtraction difference signal below a threshold level (block 404 in FIG. 26). Image threshold provides a black and white mask (on/off) that is applied to the tear film image being processed to assist in removing residual information that may not be significant enough to be analyzed and/or may contribute to inaccuracies in analysis of the tear film. The threshold value used may be provided as part of a threshold value setting provided by a clinician as part of the pre-processing settings 364, as illustrated in the system diagram of FIG. 25A. For example, the GUI utility 380 in FIG. 27 includes a compute threshold selection box 472 that may be selected to perform thresholding, where the threshold brightness level can be selected via the threshold value slide 474. The combined tear film image of FIG. 12 is copied and converted to grayscale. The grayscale image has a threshold applied according to the threshold setting to obtain a binary (black/white) image that will be used to mask the combined tear film image of FIG. 11. After the mask is applied to the combined tear film image of FIG. 11, the new combined tear film image is stored in RAM(s) 358. The areas of the tear film image that do not meet the threshold brightness level are converted to black as a result of the threshold mask.

FIGS. 29A and 29B illustrate examples of threshold masks for the combined tear film provided in FIG. 11. FIG. 29A illustrates a threshold mask 522 for a threshold setting of 70 counts out of a full scale level of 255 counts. FIG. 29B illustrates a threshold mask 524 for a threshold setting of 50. Note that the threshold mask 522 in FIG. 29A contains less portions of the combined tear film image, because the threshold setting is higher than for the threshold mask 524 of FIG. 29B. When the threshold mask according to a threshold setting of 70 is applied to the exemplary combined tear film image of FIG. 11, the resulting tear film image is illustrated FIG. 30. Much of the residual subtracted background image that surrounds the area or region of interest has been masked away.

Erode and Dilate

Another optional pre-processing function that may be applied to the resulting image or each image in a video of images of the tear film to correct anomalies in the combined tear film image(s) is the erode and dilate functions (block 406 in FIG. 26). The erode function generally removes small anomaly artifacts by subtracting objects with a radius smaller than an erode setting (which is typically in number of pixels) removing perimeter pixels where interference information may not be as distinct or accurate. The erode function may be selected by a clinician in the GUI utility 380 (see FIG. 27) by selecting the erode selection box 476. If selected, the number of pixels for erode can be provided in an erode pixels text box 478. Dilating generally connects areas that are separated by spaces smaller than a minimum dilate size setting by adding pixels of the eroded pixel data values to the perimeter of each image object remaining after the erode function is applied. The dilate function may be selected by a clinician in the GUI utility 380 (see FIG. 27) by providing the number of pixels for dilating in a dilate pixels text box 480. Erode and dilate can be used to remove small region anomalies in the resulting tear film image prior to analyzing the interference interactions to reduce or avoid inaccuracies. The inaccuracies may include those caused by bad pixels of the video camera 198 or from dust that may get onto a scanned image, or more commonly, spurious specular reflections such as: tear film meniscus at the juncture of the eyelids, glossy eyelash glints, wet skin tissue, etc. FIG. 31 illustrates the resulting tear film image of FIG. 30 after erode and dilate functions have been applied and the resulting tear film image is stored in RAM(s) 358. As illustrated therein, pixels previously included in the tear film image that was not in the tear film area or region of interest are removed. This prevents data in the image outside the area or region of interest from affecting the analysis of the resulting tear film image(s).

Removing Blinks/Other Anomalies

Another optional pre-processing function that may be applied to the resulting image or each image in a video of images of the tear film to correct anomalies in the resulting tear film image is to remove frames from the resulting tear film image that include patient blinks or significant eye movements (block 408 in FIG. 26). As illustrated in FIG. 26, blink detection is shown as being performed after a threshold and erode and dilate functions are performed on the tear film image or video of images. Alternatively, the blink detection could be performed immediately after background subtraction, such that if a blink is detected in a given frame or frames, the image in such frame or frames can be discarded and not pre-processed. Not pre-processing images where blinks are detected may increase the overall speed of pre-processing. The remove blinks or movement pre-processing may be selectable, depending upon if determining a blink, partial or complete, is the area of interest for a particular study session. For example, the GUI utility 380 in FIG. 27 includes a remove blinks selection box 484 to allow a user to control whether blinks and/or eye movements are removed from a resulting image or frames of the patient's tear film prior to analysis. Blinking of the eyelids covers the ocular tear film, and thus does not produce interference signals representing specularly reflected light from the tear film. If frames containing whole or partial blinks obscuring the area or region of interest in the patient's tear film are not removed, in the instances where the TFLT was the ROI (or area of interest), it would introduce errors in the analysis of the interference signals to determine characteristics of the TFLT of the patient's ocular tear film. Further, frames or data with significant eye movement between sequential images or frames can be removed during the detect blink pre-processing function. Large eye movements could cause inaccuracy in analysis of a patient's tear film when employing subtraction techniques to remove background signal, because subtraction involves subtracting frame-pairs in an image that closely match spatially. Thus, if there is significant eye movement between first and second images that are to be subtracted, frame pairs may not be closely matched spatially thus inaccurately removing background signal, and possibly removing a portion of the interference image of specularly reflected light from the tear film.

Different techniques can be used to determine blinks in an ocular tear film image and remove the frames as a result. For example, in one embodiment, the control system 340 directs the pre-processing system 360 to review the stored frames of the resulting images of the tear film to monitor for the presence of an eye pupil using pattern recognition. A Hough Circle Transform may be used to detect the presence of the eye pupil in a given image or frame. If the eye pupil is not detected, it is assembled such that the image or frame contains an eye blink and thus should be removed or ignored during pre-processing from the resulting image or video of images of the tear film. The resulting image or video of images can be stored in RAM(s) 358 for subsequent processing and/or analyzation.

In this regard, in one embodiment, detecting eye blinks in an ocular tear film image or frame by detecting the pupil and removing desired blink frames that do not contain an image of the pupil as a result may be performed as follows. First, ocular tear film frame pairs, one containing specularly reflected light and background signal (i.e., frame 1), and the other containing background signal (i.e., frame 2) are added together to provide a resultant image (i.e., frame 1+[frame 2−frame 1]). A grayscale is created of the resultant image, for example using an 8-bit, 255 value scale. Providing a grayscale of the resultant image allows enhanced identification of darker pixels as opposed to lighter pixels, to try to identify pixels associated with the pupil, as a non-limiting examples. As discussed above, determining that a pupil is in an ocular tear film image is one direct indication of whether the ocular tear film frame contains a partial or full eye blink. Thereafter in this example, the darkest pixel in resultant grayscale frame is found. Then, all pixels within a given intensity count are found (e.g., within 7). These are the darkest areas of the frame and include the pupil. A binary resultant frame is then created with resultant grayscale frame to transform the darker pixels to white color. That binary resultant frame is then eroded and dilated (similar to as discussed in other examples herein for tear film measurement purposes) using a sample disk. The larger or largest contiguous pixels having white color are found in the resultant binary frame. A check is next made to make sure that larger or largest contiguous pixels having white color contain at least a desired minimum number of pixels (e.g., 3000) and have a desired eccentricity (e.g., 0.8 or lower). If so, this larger or largest contiguous pixels having white color are deemed to be the pupil. If a previous frame from the current frame was also deemed to contain the pupil by ensuring the centroid of the larger or largest contiguous pixels did not shift by more than a designated number of pixels (e.g., 50 pixels), then the current frame is deemed to contain the pupil and is not rejected. If the current frame is not deemed to contain the pupil, the frame can be rejected.

In another embodiment, blinks and significant eye movements are detected using a histogram sum of the intensity of pixels in a resulting subtracted image or frame of a first and second image of the tear film. An example of such a histogram 526 is illustrated in FIG. 32. The resulting or subtracted image can be converted to grayscale (i.e., 255 levels) and a histogram generated with the gray levels of the pixels. In the histogram 526 of FIG. 32, the x-axis contains gray level ranges, and the number of pixels falling within each gray level is contained in the y-axis. The total of all the histogram 526 bins are summed. In the case of two identical frames that are subtracted, the histogram sum would be zero. However, even without an eye blink or significant eye movement, two sequentially captured frames of the patient's eye and the interference signals representing the specularly reflected light from the tear film are not identical. However, frame pairs with little movement will have a low histogram sum, while frame pairs with greater movement will yield a larger histogram sum. If the histogram sum is beyond a pre-determined threshold, an eye blink or large eye movement can be assumed and the image or frame removed. For example, the GUI utility 380 illustrated in FIG. 27 includes a histogram sum slide bar 486 that allows a user to set the threshold histogram sum. The threshold histogram sum for determining whether a blink or large eye movement should be assumed and thus the image removes from analysis of the patient's tear film can be determined experimentally, or adaptively over the course of a frame playback, assuming that blinks occur at regular intervals.

An advantage of a histogram sum of intensity method to detect eye blinks or significant eye movements is that the calculations are highly optimized as opposed to pixel-by-pixel analysis, thus assisting with real-time processing capability. Further, there is no need to understand the image structure of the patient's eye, such as the pupil or the iris details. Further, the method can detect both blinks and eye movements.

In this regard, in one embodiment, detecting eye blinks in an ocular tear film image or frame based on an intensity method may be performed as follows. First, the ocular tear film frame pairs, one containing specularly reflected light and background signal (i.e., frame 1), and the other containing background signal (i.e., frame 2) are subtracted from each other to provide a resultant image (i.e., [frame 2−frame 1]). A grayscale is created of the resultant image (e.g., 8-bits, 255 sample levels). A histogram is then calculated for the resultant grayscale image by, for example, dividing intensity in the resultant grayscale image into a desired number of bins (e.g., 64 bins of 4 counts each). The height of the tallest bin is set to a defined level (e.g., 200) and the scale of all other bins adjusted accordingly. All scaled bins are summed and compared to a predefined limit (e.g., 1000). If histogram sum is greater than this predefined limit, the resultant frame is rejected as a frame having a blink.

To remove blink islands, trains or sequences of consecutive non-blink frames bookended by blink frames can be identified. If a train consists of three or fewer non-blink frames, those frames can be rejected as blink frames. The centroid of each resultant subtracted frame is calculated to find the location of each non-blink pixel (e.g., find the average location in X-Y coordinates of center of non-blink pixel). A bounding box of each resultant subtracted frame is also calculated. The average centroid location is calculated for all non-blink frames. The average bounding box location is calculated for all non-blink frames. If the centroid for a given frame deviates from the average centroid location for all frames by more than a defined number of pixels (e.g., 30) up, down, or temporally (from temple or nose of patient), then that frame can be rejected as a blink frame. If top, bottom, or temporal edges of a bounding box deviate from the average bounding box location by more than 30 pixels, the frame can be rejected as a blink frame. The blink island removal process can be repeated by labeling blink islands as either blink or non-blink islands. Optionally, a first number of frames (e.g., 5) may be removed as well from the frame sequence after each blink to allow tear film to stabilize before quantifying lipid layer thickness.

Another alternate technique to detect blinks in the tear film image or video of images for possible removal is to calculate a simple average gray level in an image or video of images. Because the subtracted, resulting images of the tear film subtract background signal, and have been processed using a threshold mask, and erode and dilate functions performed in this example, the resulting images will have a lower average gray level due to black areas present than if a blink is present. A blink contains skin color, which will increase the average gray level of an image containing a blink. A threshold average gray level setting can be provided. If the average gray level of a particular frame is below the threshold, the frame is ignored from further analysis or removed from the resulting video of frames of the tear film.

Another alternate technique to detect blinks in an image or video of images for removal is to calculate the average number of pixels in a given frame that have a gray level value below a threshold gray level value. If the percentage of pixels in a given frame is below a defined threshold percentage, this can be an indication that a blink has occurred in the frame, or that the frame is otherwise unworthy of consideration when analyzing the tear film. Alternatively, a spatial frequency calculation can be performed on a frame to determine the amount of fine detail in a given frame. If the detail present is below a threshold detail level, this may be an indication of a blink or other obscurity of the tear film, since skin from the eyelid coming down and being captured in a frame will have less detail than the subtracted image of the tear film. A histogram can be used to record any of the above-referenced calculations to use in analyzing whether a given frame should be removed from the final pre-processed resulting image or images of the tear film for analyzation.

A partial blink detection method may also be performed to determine the effective blinking of a patient, which will be discussed in examples below. A partial blink detection method may be used alone or in combination with blink detection methods, including those described above. In this regard, in one embodiment, a partial eye blink detection method in an ocular tear film image or frame may be performed as follows. For example, to detect partial blinking, a first master frame may first be created from a first frame of a frame pair of a blink frame sequence of the ocular tear film to track pixels and whether they change as an eyelid passes during a blink. For the first added color frame of a blink (identified using one of the above blink detection methods as an example), the chroma and intensity of each pixel is calculated. The chroma is equal to maximum RGB value minus minimum RGB value. The intensity is provided as R²+G²+B². If a pixel has a chroma less than or equal to a predefined value (e.g., 25) and an intensity greater than a predefined value (e.g. 300), the corresponding pixel on the first frame of the ocular tear film is set to white color value. This means that this pixel is part of the specular reflection and has not been covered by the eyelid. Next, the master frame can be eroded with a disk of a desired radius (e.g., 5). If any pixels in the second frame no longer meet the intensity and chroma criteria within the master frame (i.e. they are no longer showing specular reflection), the corresponding pixel is set to black color value in the master frame. The above process is then repeated for a blink sequence of frames until completed. The number of pixels present in the master frame that are still white are calculated, meaning these pixels were not covered by the eyelid at any point during blink sequence. The number of white pixels is compared to a preset threshold (e.g., 0). If the number of uncovered pixels in the master frame is greater than this threshold, the detected blink is labeled a partial blink.

As will be discussed in more detail below, the identification of partial blinks allows the ratio of partial blinks to full blinks to be determined to provide a blink efficiency for a patient.

ICC Profiling

Pre-processing of the resulting tear film image(s) may also optionally include applying an International Colour Consortium (ICC) profile to the pre-processed interference images of the tear film (block 410, FIG. 26). FIG. 33 illustrates an optional process of loading an ICC profile into an ICC profile 531 in the control system 340 (block 530). In this regard, the GUI utility 380 illustrated in FIG. 27 also includes an apply ICC box 492 that can be selected by a clinician to load the ICC profile 531. The ICC profile 531 may be stored in memory in the control system 340, including in RAM(s) 358. In this manner, the GUI utility 380 in FIG. 27 also allows for a particular ICC profile 531 to be selected for application in the ICC profile file text box 494. The ICC profile 531 can be used to adjust color reproduction from scanned images from cameras or other devices into a standard red-green-blue (RGB) color space (among other selectable standard color spaces) defined by the ICC and based on a measurement system defined internationally by the Commission Internationale de l'Eclairage (CIE). Adjusting the pre-processed resulting tear film interference images corrects for variations in the camera color response and the light source spectrum and allows the images to be compatibly compared with a tear film layer interference model to measure the thickness of a TFLT, as will be described later in this application. The tear film layers represented in the tear film layer interference model can be LLTs, ALTs, or both, as will be described in more detail below.

In this regard, the ICC profile 531 may have been previously loaded to the OSI device 170 before imaging of a patient's tear film and also applied to a tear film layer interference model when loaded into the OSI device 170 independent of imaging operations and flow. As will be discussed in more detail below, a tear film layer interference model in the form of a TFLT palette 533 containing color values representing interference interactions from specularly reflected light from a tear film for various LLTs and ALTs can also be loaded into the OSI device 170 (block 532 in FIG. 36). The TFLT palette 533 contains a series of color values that are assigned LLTs and/or ALTs based on a theoretical tear film layer interference model to be compared against the color value representations of interference interactions in the resulting image(s) of the patient's tear film. When applying the optional ICC profile 531 to the

TFLT palette 533 (block 534 in FIG. 33), the color values in both the tear film layer interference model and the color values representing interference interactions in the resulting image of the tear film are adjusted for a more accurate comparison between the two to measure LLT and/or ALT.

Brightness

Also as an optional pre-processing step, brightness and red-green-blue (RGB) subtract functions may be applied to the resulting interference signals of the patient's tear film before post-processing for analysis and measuring TFLT is performed (blocks 412 and 414 in FIG. 26). The brightness may be adjusted pixel-by-pixel by selecting the adjust brightness selection box 504 according to a corresponding brightness level value provided in a brightness value box 506, as illustrated in the GUI utility 380 of FIG. 27. When the brightness value box 506 is selected, the brightness of each palette value of the TFLT palette 533 is also adjusted accordingly.

RGB Subtraction (Normalization)

The RGB subtract function subtracts a DC offset from the interference signal in the resulting image(s) of the tear film representing the interference interactions in the interference signal. An RGB subtract setting may be provided from the pre-processing settings 364 to apply to the interference signal in the resulting image of the tear film to normalize against. As an example, the GUI utility 380 in FIG. 27 allows an RGB offset to be supplied by a clinician or other technician for use in the RGB subtract function. As illustrated therein, the subtract RGB function can be activated by selecting the RGB subtract selection box 496. If selected, the individual RGB offsets can be provided in offset value input boxes 498. After pre-processing is performed, if any, on the resulting image, the resulting image can be provided to a post-processing system to measure TLFT (block 416), as discussed later below in this application.

Displaying Images

The resulting images of the tear film may also be displayed on the display 174 of the OSI device 170 for human diagnosis of the patient's ocular tear film. The OSI device 170 is configured so that a clinician can display and see the raw captured image of the patient's eye 192 by the video camera 198, the resulting images of the tear film before pre-processing, or the resulting images of the tear film after pre-processing. Displaying images of the tear film on the display 174 may entail different settings and steps. For example, if the video camera 198 provides linear images of the patient's tear film, the linear images must be converted into a non-linear format to be properly displayed on the display 174. In this regard, a process that is performed by the visualization system 370 according to one embodiment is illustrated in FIG. 34.

As illustrated in FIG. 34, the video camera 198 has already taken the first and second images of a patient's ocular tear film as previously illustrated in FIGS. 9 and 10, and provided the images to the video acquisition system 356. The frames of the first and second images were then loaded into RAM(s) 358 by the video acquisition system 356. Thereafter, as illustrated in FIG. 34, the control system 340 commands the visualization system 370 to process the first and second images to prepare them for being displayed on the display 174, 538. In this regard, the visualization system 370 loads the first and second image frames of the ocular tear film from RAM(s) 358 (block 535). The previously described subtraction technique is used to remove background signal from the interference interactions of the specularly reflected light from the tear film, as previously described above and illustrated in FIG. 11. The first image(s) is subtracted from the second image(s) to remove background signal in the illuminated portions of the first image(s), and vice versa, and the subtracted images are then combined to produce an interference interaction of the specularly reflected light of the entire area or region of interest of the tear film, as previously discussed and illustrated in FIG. 11 (block 536 in FIG. 34).

Again, for example, this processing could be performed using the Matlab® function “cvAbsDiff.” Before being displayed, the contrast and saturation levels for the resulting images can be adjusted according to contrast and saturation settings provided by a clinician via the user interface system 378 and/or programmed into the visualization system 370 (block 537). For example, the GUI utility 380 in FIG. 27 provides an apply contrast button 464 and a contrast setting slide 466 to allow the clinician to set the contrast setting in the display settings 374 for display of images on the display 174. The GUI utility 380 also provides an apply saturation button 468 and a saturation setting slide 469 to allow a clinician to set the saturation setting in the display settings 374 for the display of images on the display 174. The images can then be provided by the visualization system 370 to the display 174 for displaying (block 538 in FIG. 34). Also, any of the resulting images after pre-processing steps in the pre-processing system 360 can be provided to the display 174 for processing.

FIGS. 35A-35C illustrate examples of different tear film images that are displayed on the display 174 of the OSI device 170. FIG. 35A illustrates a first image 539 of the patient's tear film showing the pattern captured by the video camera 198. This image is the same image as illustrated in FIG. 9 and previously described above, but processed from a linear output from the video camera 198 to be properly displayed on the display 174. FIG. 35B illustrates a second image 540 of the patient's tear film illustrated in FIG. 10 and previously described above. FIG. 35C illustrates a resulting “overlaid” image 341 of the first and second images 539, 540 of the patient's tear film and to provide interference interactions of the specularly reflected light from the tear film over the entire area or region of interest. This is the same image as illustrated in FIG. 11 and previously described above.

In this example, the original number of frames of the patient's tear film captured can be reduced if frames in the subtracted image frames capture blinks or erratic movements, and these frames are eliminated in pre-processing, a further reduction in frames will occur during pre-processing from the number of images raw captured in images of the patient's tear film. Although these frames are eliminated from being further processed, they can be retained for visualization rendering a realistic and natural video playback. Further, by applying a thresholding function and erode and dilating functions, the number of non-black pixels which contain TLFT interference information is substantially reduced as well. Thus, the amount of pixel information that is processed by the post-processing system 362 is reduced, and may be on the order of 70% less information to process than the raw image capture information, thereby pre-filtering for the desired interference ROI and reducing or elimination potentially erroneous information as well as allowing for faster analysis due to the reduction in information.

At this point, the resulting images of the tear film have been pre-processed by the pre-processing system 360 according to whatever pre-processing settings 364 and pre-processing steps have been selected or implemented by the control system 340. The resulting images of the tear film are ready to be processed for analyzing and determining TFLT. In this example, this is performed by the post-processing system 362 in FIG. 25A and is based on the post-processing settings 366 also illustrated therein. An embodiment of the post-processing performed by the post-processing system 362 is illustrated in the flowchart of FIG. 36.

Tear Film Interference Models

As illustrated in FIG. 36, pre-processed images 543 of the resulting images of the tear film are retrieved from RAM(s) 358 where they were previously stored by the pre-processing system 360. Before discussing the particular embodiment of the post-processing system 362 in FIG. 36, in general, to measure TFLT, the RGB color values of the pixels in the resulting images of the tear film are compared against color values stored in a tear film interference model that has been previously loaded into the OSI device 170 (see FIG. 33. The tear film interference model may be stored as a TFLT palette 533 containing RGB values representing interference colors for given LLTs and/or ALTs. The TFLT palette contains interference color values that represent TFLTs based on a theoretical tear film interference model in this embodiment. Depending on the TFLT palette provided, the interference color values represented therein may represent LLTs, ALTs, or both. An estimation of TFLT for each ROI pixel is based on this comparison. This estimate of TFLT is then provided to the clinician via the display 174 and/or recorded in memory to assist in diagnosing DES.

Before discussing embodiments of how the TFLTs are estimated from the pre-processed resulting image colored interference interactions resulting from specularly reflected light from the tear film, tear film interference modeling is first discussed. Tear film interference modeling can be used to determine an interference color value for a given TFLT to measure TFLT, which can include both LLT and/or ALT.

Although the interference signals representing specularly reflected light from the tear film are influenced by all layers in the tear film, the analysis of interference interactions due to the specularly reflected light can be analyzed under a 2-wave tear film model (i.e., two reflections) to measure LLT. A 2-wave tear film model is based on a first light wave(s) specularly reflecting from the air-to-lipid layer transition of a tear film and a second light wave specularly reflecting from the lipid layer-to-aqueous layer transition of the tear film. In the 2-wave model, the aqueous layer is effective ignored and treated to be of infinite thickness. To measure LLT using a 2-wave model, a 2-wave tear film model was developed wherein the light source and lipid layers of varying thicknesses were modeled mathematically. To model the tear-film interference portion, commercially available software, such as that available by FilmStar and Zemax as examples, allows image simulation of thin films for modeling. Relevant effects that can be considered in the simulation include refraction, reflection, phase difference, polarization, angle of incidence, and refractive index wavelength dispersion. For example, a lipid layer could be modeled as having an index of refraction of 1.48 or as a fused silica substrate (SiO₂) having a 1.46 index of refraction. A back material, such as Magnesium Flouride (MgF₂) having an index of refraction of 1.38 may be used to provide a 2-wave model of air/SiO₂/MgF₂ (1.0/1.46/1.38). To obtain the most accurate modeling results, the model can include the refractive index and wavelength dispersion values of biological lipid material and biological aqueous material, found from the literature, thus to provide a precise two-wave model of air/lipid/aqueous layers. Thus, a 2-wave tear film interference model allows measurement of LLT regardless of ALT.

Simulations can be mathematically performed by varying the LLT between 10 to 300 nm. As a second step, the RGB color values of the resulting interference signals from the modeled light source causing the modeled lipid layer to specularly reflected light and received by the modeled camera were determined for each of the modeled LLT. These RGB color values representing interference interactions in specularly reflected light from the modeled tear film were used to form a 2-wave model LLT palette, wherein each RGB color value is assigned a different LLT. The resulting subtracted image of the first and second images from the patient's tear film containing interference signals representing specularly reflected light are compared to the RGB color values in the 2-wave model LLT palette to measure LLT.

In another embodiment, a 3-wave tear film interference model may be employed to estimate LLT. A 3-wave tear film interference model does not assume that the aqueous layer is infinite in thickness. In an actual patient's tear film, the aqueous layer is not infinite. The 3-wave tear film interference model is based on both the first and second reflected light waves of the 2-wave model and additionally light wave(s) specularly reflecting from the aqueous-to-mucin layer and/or cornea transitions. Thus, a 3-wave tear film interference model recognizes the contribution of specularly reflected light from the aqueous-to-mucin layer and/or cornea transition that the 2-wave tear film interference model does not. To estimate LLT using a 3-wave tear film interference model, a 3-wave tear film model was previously constructed wherein the light source and a tear film of varying lipid and aqueous layer thicknesses were mathematically modeled. For example, a lipid layer could be mathematically modeled as a material having an index of refraction of 1.48 or as fused silica substrate (SiO₂), which has a 1.46 index of refraction. Different thicknesses of the lipid layer can be simulated. A fixed thickness aqueous layer (e.g., >=2 μm) could be mathematically modeled as Magnesium Flouride (MgF₂) having an index of refraction of 1.38. A biological cornea could be mathematically modeled as fused silica with no dispersion, thereby resulting in a 3-wave model of air/SiO₂/MgF₂/SiO₂ (i.e., 1.0/1.46/1.38/1.46 with no dispersion). As before, accurate results are obtained if the model can include the refractive index and wavelength dispersion values of biological lipid material, biological aqueous material, and cornea tissue, found from the literature, thus to provide a precise two-wave model of air/lipid/aqueous/cornea layers. The resulting interference interactions of specularly reflected light from the various LLT values and with a fixed ALT value are recorded in the model and, when combined with modeling of the light source and the camera, will be used to compare against interference from specularly reflected light from an actual tear film to measure LLT and/or ALT.

In another embodiment of the OSI device 170 and the post-processing system 362 in particular, a 3-wave tear film interference model is employed to estimate both LLT and ALT. In this regard, instead of providing either a 2-wave theoretical tear film interference model that assumes an infinite aqueous layer thickness or a 3-wave model that assumes a fixed or minimum aqueous layer thickness (e.g., ≧2 μm), a 3-wave theoretical tear film interference model is developed that provides variances in both LLT and ALT in the mathematical model of the tear film. Again, the lipid layer in the tear film model could be modeled mathematically as a material having an index of refraction of 1.48 or as fused silica substrate (SiO₂) having a 1.46 index of refraction. The aqueous layer could be modeled mathematically as Magnesium Flouride (MgF₂) having an index of refraction of 1.38. A biological cornea could be modeled as fused silica with no dispersion, thereby resulting in a 3-wave model of air/SiO₂/MgF₂/SiO₂ (no dispersion). Once again, the most accurate results are obtained if the model can include the refractive index and wavelength dispersion values of biological lipid material, biological aqueous material, and cornea tissue, found from the literature, thus to provide a precise two-wave model of air/lipid/aqueous/cornea layers. Thus, a two-dimensional (2D) TFLT palette 560 (FIG. 37A) is produced for analysis of interference interactions from specularly reflected light from the tear film. One dimension of the TFLT palette 560 represents a range of RGB color values each representing a given theoretical LLT calculated by mathematically modeling the light source and the camera and calculating the interference interactions from specularly reflected light from the tear film model for each variation in LLT 564 in the tear film interference model. A second dimension of the TFLT palette 560 represents ALT also calculated by mathematically modeling the light source and the camera and calculating the interference interactions from specularly reflected light from the tear film interference model for each variation in ALT 562 at each LLT value 564 in the tear film interference model.

Post-Processing/TFLT Measurement

To measure TFLT, a spectral analysis of the resulting interference signal or image is performed during post-processing to calculate a TFLT. In one embodiment, the spectral analysis is performed by performing a look-up in a tear film interference model to compare one or more interference interactions present in the resulting interference signal representing specularly reflected light from the tear film to the RGB color values in the tear film interference model. In this regard, FIGS. 37A and 37B illustrate two examples of palette models for use in post-processing of the resulting image having interference interactions from specularly reflected light from the tear film using a 3-wave theoretical tear film interference model developed using a 3-wave theoretical tear film model. In general, an RGB numerical value color scheme is employed in this embodiment, wherein the RGB value of a given pixel from a resulting pre-processed tear film image of a patient is compared to RGB values in the 3-wave tear film interference model representing color values for various LLTs and ALTs in a 3-wave modeled theoretical tear film. The closest matching RGB color is used to determine the LLT and/or ALT for each pixel in the resulting signal or image. All pixels for a given resulting frame containing the resulting interference signal are analyzed in the same manner on a pixel-by-pixel basis. A histogram of the LLT and ALT occurrences is then developed for all pixels for all frames and the average LLT and ALT determined from the histogram (block 548 in FIG. 36).

FIG. 37A illustrates an exemplary TFLT palette 560 in the form of colors representing the included RGB color values representing interference of specularly reflected light from a 3-wave theoretical tear film model used to compared colors from the resulting image of the patient's tear film to estimate LLT and ALT. FIG. 37B illustrates an alternative example of a TFLT palette 560′ in the form of colors representing the included RGB color values representing interference of specularly reflected light from a 3-wave theoretical tear film model used to compare colors from the resulting image of the patient's tear film to estimate LLT and ALT. As illustrated in FIG. 37A, the TFLT palette 560 contains a plurality of hue colors arranged in a series of rows 562 and columns 564. In this example, there are 144 color hue entries in the TFLT palette 560, with nine (9) different ALTs and sixteen (16) different LLTs in the illustrated TFLT palette 560, although another embodiment includes thirty (30) different LLTs. Providing any number of LLT and TFLT increments is theoretically possible. The columns 564 in the TFLT palette 560 contain a series of LLTs in ascending order of thickness from left to right. The rows 562 in the TFLT palette 560 contain a series of ALTs in ascending order of thickness from top to bottom. The sixteen (16) LLT increments provided in the columns 564 in the TFLT palette 560 are 25, 50, 75, 80, 90, 100, 113, 125, 138, 150, 163, 175, 180, 190, 200, and 225 nanometers (nm). The nine (9) ALT increments provided in the rows 562 in the TFLT palette 560 are 0.25, 0.5, 0.75, 1.0, 1.25, 1.5, 1.75, 3.0 and 6.0 μm. As another example, as illustrated in FIG. 37B, the LLTs in the columns 564′ in the TFLT palette 560′ are provided in increments of 10 nm between 0 nm and 160 nm. The nine (9) ALT increments provided in the rows 562′ in the TFLT palette 560 are 0.3, 0.5, 0.8, 1.0, 1.3, 1.5, 1.8, 2.0 and 5.0 μm.

As part of a per pixel LLT analysis 544 provided in the post-processing system 362 in FIG. 36, for each pixel in each of the pre-processed resulting images of the area or region of interest in the tear film, a closest match determination is made between the RGB color of the pixel to the nearest RGB color in the TFLT palette 560 (block 545 in FIG. 36). The ALTs and LLTs for that pixel are determined by the corresponding ALT thickness in the y-axis of the TFLT palette 560, and the corresponding LLT thickness in the x-axis of the TFLT palette 560. As illustrated in FIG. 37, the TFLT palette 560 colors are actually represented by RGB values. The pixels in each of the pre-processed resulting images of the tear film are also converted and stored as RGB values, although any other color representation can be used as desired, as long as the palette and the image pixel data use the same representational color space. FIG. 38 illustrates the TFLT palette 560 in color pattern form with normalization applied to each red-green-blue (RGB) color value individually. Normalizing a TFLT palette is optional. The TFLT palette 560 in FIG. 38 is displayed using brightness control (i.e., normalization, as previously described) and without the RGB values included, which may be more visually pleasing to a clinician if displayed on the display 174. The GUI utility 380 allows selection of different palettes by selecting a file in the palette file drop down 502, as illustrated in FIG. 27, each palette being specific to the choice of 2-wave vs. 3-wave mode, the chosen source's spectrum, and the chosen camera's RGB spectral responses. To determine the closest pixel color in the TFLT palette 560, a Euclidean distance color difference equation is employed to calculate the distance in color between the RGB value of a pixel from the pre-processed resulting image of the patient's tear film and RGB values in the TFLT palette 560 as follows below, although other embodiments of the present disclosure are not so limited:

Diff.=√((Rpixel−Rpalette)²⁺ (G _(pixel) −Gpalette)²⁺ (B _(pixel) −B _(palette))²)

Thus, the color difference is calculated for all palette entries in the TFLT palette 560. The corresponding LLT and ALT values are determined from the color hue in the TFLT palette 560 having the least difference from each pixel in each frame of the pre-processed resulting images of the tear film. The results can be stored in RAM(s) 358 or any other convenient storage medium. To prevent pixels without a close match to a color in the TFLT palette 560 from being included in a processed result of LLT and ALT, a setting can be made to discard pixels from the results if the distance between the color of a given pixel is not within the entered acceptable distance of a color value in the TFLT palette 560 (block 546 in FIG. 36). The GUI utility 380 in FIG. 27 illustrates this setting such as would be the case if made available to a technician or clinician. A distance range input box 508 is provided to allow the maximum distance value to be provided for a pixel in a tear film image to be included in LLT and ALT results. Alternatively, all pixels can be included in the LLT and ALT results by selecting the ignore distance selection box 510 in the GUI utility 380 of FIG. 27.

Each LLT and ALT determined for each pixel from a comparison in the TFLT palette 560 via the closest matching color that is within a given distance (if that post-processing setting 366 is set) or for all LLT and ALT determined values are then used to build a TFLT histogram. The TFLT histogram is used to determine a weighted average of the LLT and ALT values for each pixel in the resulting image(s) of the patient's tear film to provide an overall estimate of the patient's LLT and ALT. FIG. 39 illustrates an example of such a TFLT histogram 460. This TFLT histogram 570 may be displayed as a result of the shown LLT histogram selection box 500 being selected in the GUI utility 380 of FIG. 27. As illustrated therein, for each pixel within an acceptable distance, the TFLT histogram 570 is built in a stacked fashion with determined ALT values 574 stacked for each determined LLT value 572 (block 549 in FIG. 36). Thus, the TFLT histogram 570 represents LLT and ALT values for each pixel. A horizontal line separates each stacked ALT value 574 within each LLT bar.

One convenient way to determine the final LLT and ALT estimates is with a simple weighted average of the LLT and ALT values 572, 574 in the TFLT histogram 570. In the example of the TFLT histogram 570 in FIG. 39, the average LLT value 576 was determined to be 90.9 nm. The number of samples 578 (i.e., pixels) included in the TFLT histogram 570 was 31,119. The frame number 580 indicates which frame of the resulting video image is being processed, since the TFLT histogram 570 represents a single frame result, or the first of a frame pair in the case of background subtraction. The maximum distance 582 between the color of any given pixel among the 31,119 pixels and a color in the TFLT palette 560 was 19.9, 20 may have been the set limit (Maximum Acceptable Palette Distance) for inclusion of any matches. The average distance 584 between the color of each of the 31,119 pixels and its matching color in the TFLT palette 560 was 7.8. The maximum distance 582 and average distance 584 values provide an indication of how well the color values of the pixels in the interference signal of the specularly reflected light from the patient's tear film match the color values in the TFLT palette 560. The smaller the distance, the closer the matches. The TFLT histogram 570 can be displayed on the display 174 to allow a clinician to review this information graphically as well as numerically. If either the maximum distance 582 or average distance 584 values are too high, this may be an indication that the measured LLT and ALT values may be inaccurate, or that the image normalization is not of the correct value. Further imaging of the patient's eye and tear film, or system recalibration can be performed to attempt to improve the results. Also, a histogram 586 of the LLT distances 588 between the pixels and the colors in the TFLT palette 560 can be displayed as illustrated in FIG. 40 to show the distribution of the distance differences to further assist a clinician in judgment of the results.

Other results can be displayed on the display 174 of the OSI device 170 that may be used by a physician or technician to judge the LLT and/or ALT measurement results. For example, FIG. 41 illustrates a threshold window 590 illustrating a (inverse) threshold mask 592 that was used during pre-processing of the tear film images. In this example, the threshold window 590 was generated as a result of the show threshold window selection box 482 being selected in the GUI utility 380 of FIG. 27. This may be used by a clinician to humanly evaluate whether the threshold mask looks abnormal. If so, this may have caused the LLT and ALT estimates to be inaccurate and may cause the clinician to discard the results and image the patient's tear film again. The maximum distance between the color of any given pixel among the 31,119 pixels and a color in the TFLT palette 560 was 19.9 in this example.

FIG. 42 illustrates another histogram that may be displayed on the display 174 and may be useful to a clinician. As illustrated therein, a three-dimensional (3D) histogram plot 460 is illustrated. The clinician can choose whether the OSI device 170 displays this histogram plot 460 by selecting the 3D plot selection box 516 in the GUI utility 380 of FIG. 27, as an example, or the OSI device 170 may automatically display the histogram plot 460. The 3D histogram plot 460 is simply another way to graphically display the fit of the processed pixels from the pre-processed images of the tear film to the TFLT palette 560. The plane defined by the LLT 596 and ALT 598 axes represents the TFLT palette 560. The axis labeled “Samples” 600 is the number of pixels that match a particular color in the TFLT palette 560.

FIG. 43 illustrates a result image 594 of the specularly reflected light from a patient's tear film. However, the actual pixel value for a given area on the tear film is replaced with the determined closest matching color value representation in the TFLT palette 560 to a given pixel for that pixel location in the resulting image of the patient's tear film (block 547 in FIG. 36). This setting can be selected, for example, in the GUI utility 380 of FIG. 27. Therein, a “replace resulting image . . . ” selection box 512 is provided to allow a clinician to choose this option. Visually displaying interference interactions representing the closest matching color value to the interference interactions in the interference signal of the specularly reflected light from a patient's tear film in this manner may be helpful to determine how closely the tear film interference model matches the actual color value representing the resulting image (or pixels in the image).

Ambiguities can arise when calculating the nearest distance between an RGB value of a pixel from a tear film image and RGB values in a TFLT palette, such as TFLT palettes 560 and 560′ in FIGS. 37A and 37B as examples. This is because when the theoretical LLT of the TFLT palette is plotted in RGB space for a given ALT in three-dimensional (3D) space, the TFLT palette 604 is a locus that resembles a pretzel like curve, as illustrated with a 2-D representation in the exemplary TFLT palette locus 606 in FIG. 44. Ambiguities can arise when a tear film image RGB pixel value has close matches to the TFLT palette locus 606 at significantly different LLT levels. For example, as illustrated in the TFLT palette locus 606 in FIG. 44, there are three (3) areas of close intersection 608, 610, 612 between RGB values in the TFLT palette locus 606 even though these areas of close intersection 608, 610, 612 represent substantially different LLTs on the TFLT palette locus 606. This is due to the cyclical phenomenon caused by increasing orders of optical wave interference, and in particular, first order versus second order interference for the LLT range in the tear films. Thus, if an RGB value of a tear film image pixel is sufficiently close to two different LLT points in the TFLT palette locus 606, the closest RGB match may be difficult to match. The closest RGB match may be to an incorrect LLT in the TFLT palette locus 606 due to error in the camera and translation of received light to RGB values. Thus, it may be desired to provide further processing when determining the closest RGB value in the TFLT palette locus 606 to RGB values of tear film image pixel values when measuring TFLT.

In this regard, there are several possibilities that can be employed to avoid ambiguous RGB matches in a TFLT palette. For example, the maximum LLT values in a TFLT palette may be limited. For example, the TFLT palette locus 606 in FIG. 44 includes LLTs between 10 nm and 300 nm. If the TFLT palette locus 606 was limited in LLT range, such as 240 nm as illustrated in the TFLT palette locus 614 in FIG. 45, two areas of close intersection 610 and 612 in the TFLT palette 604 in FIG. 44 are avoided in the TFLT palette 604 of FIG. 45. This restriction of the LLT ranges may be acceptable based on clinical experience since most patients do not exhibit tear film colors above the 240 nm range and dry eye symptoms are more problematic at thinner LLTs. In this scenario, the limited TFLT palette 604 of FIG. 45 would be used as the TFLT palette in the post-processing system 362 in FIG. 36, as an example.

Even by eliminating two areas of close intersection 610, 612 in the TFLT palette 604, as illustrated in FIG. 45, the area of close intersection 608 still remains in the TFLT palette locus 614. In this embodiment, the area of close intersection 608 is for LLT values near 20 nm versus 180 nm. In these regions, the maximum distance allowed for a valid RGB match is restricted to a value of about half the distance of the TFLT palette's 604 nearing ambiguity distance. In this regard, RGB values for tear film pixels with match distances exceeding the specified values can be further excluded from the TFLT calculation to avoid tear film pixels having ambiguous corresponding LLT values for a given RGB value to avoid error in TFLT measurement as a result.

In this regard, FIG. 46 illustrates the TFLT palette locus 614 in FIG. 45, but with a circle of radius R swept along the path of the TFLT palette locus 614 in a cylinder or pipe 616 of radius R. Radius R is the acceptable distance to palette (ADP), which can be configured in the control system 340. When visualized as a swept volume inside the cylinder or pipe 616, RGB values of tear film image pixels that fall within those intersecting volumes may be considered ambiguous and thus not used in calculating TFLT, including the average TFLT. The smaller the ADP is set, the more poorly matching tear film image pixels that may be excluded in TFLT measurement, but less pixels are available for use in calculation of TFLT. The larger the ADP is set, the less tear film image pixels that may be excluded in TFLT measurement, but it is more possible that incorrect LLTs are included in the TFLT measurement. The ADP can be set to any value desired. Thus, the ADP acts effectively as a filter to filter out RGB values for tear film images that are deemed a poor match and those that may be ambiguous according to the ADP setting. This filtering can be included in the post-processing system 362 in FIG. 36, as an example, and in step 546 therein, as an example.

Graphical User Interface (GUI)

In order to operate the OSI device 170, a user interface program may be provided in the user interface system 378 (see FIG. 25A) that drives various graphical user interface (GUI) screens on the display 174 of the OSI device 170 in addition to the GUI utility 380 of FIG. 27 to allow access to the OSI device 170. Some examples of control and accesses have been previously described above. Examples of these GUI screens from this GUI are illustrated in FIGS. 44-48 and described below. The GUI screens allow access to the control system 340 in the OSI device 170 and to features provided therein. As illustrated in FIG. 47, a login GUI screen 620 is illustrated. The login GUI screen 620 may be provided in the form of a GUI window 621 that is initiated when a program is executed. The login GUI screen 620 allows a clinician or other user to log into the OSI device 170. The OSI device 170 may have protected access such that one must have an authorized user name and password to gain access. This may be provided to comply with medical records and privacy protection laws. As illustrated therein, a user can enter their user name in a user name text box 622 and a corresponding password in the password text box 624. A touch or virtual keyboard 626 may be provided to allow alphanumeric entry. To gain access to help or to log out, the user can select the help and log out tabs 628, 630, which may remain resident and available on any of the GUI screens. After the user is ready to login, the user can select the submit button 632. The user name and password entered in the user name text box 622 and the password text box 624 are verified against permissible users in a user database stored in the disk memory 368 in the OSI device 170 (see FIG. 25A).

If a user successfully logs into the OSI device 170, a patient GUI screen 634 appears on the display 174 with the patient records tab 631 selected, as illustrated in FIG. 48. The patient GUI screen 634 allows a user to either create a new patient or to access an existing patient. A new patient or patient search information can be entered into any of the various patient text boxes 636 that correspond to patient fields in a patient database. Again, the information can be entered through the virtual keyboard 626, facilitated with a mouse pointing device (not shown), a joystick, or with a touch screen covering on the display 174. These include a patient ID text box 638, patient last name text box 640, patient middle initial text box 642, a patient first name text box 644, and a date of birth text box 646. This data can be entered for a new patient, or used to search a patient database on the disk memory 368 (see FIG. 25A) to access an existing patient's records. The OSI device 170 may contain disk memory 368 with enough storage capability to store information and tear film images regarding a number of patients. Further, the OSI device 170 may be configured to store patient information outside of the OSI device 170 on a separate local memory storage device or remotely. If the patient data added in the patient text boxes 636 is for a new patient, the user can select the add new patient button 652 to add the new patient to the patient database. The patients in the patient database can also be reviewed in a scroll box 648. A scroll control 650 allows up and down scrolling of the patient database records. The patient database records are shown as being sorted by last name, but may be sortable by any of the patient fields in the patient database.

If a patient is selected in the scroll box 648, which may be an existing or just newly added patient, as illustrated in the GUI screen 660 in FIG. 49, the user is provided with an option to either capture new tear film images of the selected patient or to view past images, if past tear film images are stored for the selected patient on disk memory 368. In this regard, the selected patient is highlighted 662 in the patient scroll box 648, and a select patient action pop-up box 664 is displayed. The user can either select the capture new images button 666 or the view past images button 668. If the capture new images button 666 is selected, the capture images GUI 670 is displayed to the user under the capture images tab 671 on the display 174, which is illustrated in FIG. 50. As illustrated therein, a patient eye image viewing area 672 is provided, which is providing images of the patient's eye and tear film obtained by the video camera 198 in the OSI device 170. In this example, the image is of an overlay of the subtracted first and second pattern images of the patient's tear film onto the raw image of the patient's eye and tear film, as previously discussed. The focus of the image can be adjusted via a focus control 674. The brightness level of the image in the viewing area 672 is controlled via a brightness control 676. The user can control the position of the video camera 198 to align the camera lens with the tear film of interest whether the lens is aligned with the patient's left or right eye via an eye selection control 678. Each frame of the patient's eye captured by the video camera 198 can be stepped via a stepping control 680. Optionally, or in addition, a joystick may be provided in the OSI device 170 to allow control of the video camera 198.

The stored images of the patient's eye and tear film can also be accessed from a patient history database stored in disk memory 368. FIG. 51 illustrates a patient history GUI screen 682 that shows a pop-up window 684 showing historical entries for a given patient. For each tear film imaging, a time and date stamp 685 is provided. The images of a patient's left and right eye can be shown in thumbnail views 686, 688 for ease in selection by a user. The stored images can be scrolled up and down in the pop-up window 684 via a step scroll bar 690. Label names in tag boxes 692 can also be associated with the images. Once a desired image is selected for display, the user can select the image to display the image in larger view in the capture images GUI 670 in FIG. 50. Further, two tear film images of a patient can be simultaneously displayed from any current or prior examinations for a single patient, as illustrated in FIG. 52.

As illustrated in FIG. 52, a view images GUI screen 700 is shown, wherein a user has selected a view images tab 701 to display images of a patient's ocular tear film. In this view images GUI screen 700, both images of the patient's left eye 702 and right eye 704 are illustrated side by side. In this example, the images 702, 704 are overlays of the subtracted first and second pattern images of the patients tear film onto the raw image of the patient's tear eye and tear film, as previously discussed. Scroll buttons 706, 708 can be selected to move a desired image among the video of images of the patient's eye for display in the view images GUI screen 700. Further, step and play controls 710, 712 allow the user to control playing a stored video of the patient's tear film images and stepping through the patient's tear film images one at a time, if desired. The user can also select an open patient history tab 714 to review information stored regarding the patient's history, which may aid in analysis and determining whether the patient's tear film has improved or degraded. A toggle button 715 can be selected by the user to switch the images 702, 704 from the overlay view to just the images 720, 722, of the resulting interference interactions of specularly reflected light from the patient's tear films, as illustrated in FIG. 53. As illustrated in FIG. 53, only the resulting interference interactions from the patient's tear film are illustrated. The user may select this option if it is desired to concentrate the visual examination of the patient's tear film solely to the interference interactions.

In yet another embodiment, a polarization subtraction algorithm improves isolation of a tear film interference pattern from a background signal. FIG. 54 is a flow chart that illustrates step-by-step computerized processing of the polarization subtraction algorithm of the present disclosure. A first image frame shown in FIG. 55A is automatically extracted from a polarization video segment (block 900). A second image frame shown in FIG. 55B is automatically extracted from a perpendicular polarization video segment (block 902). The polarization subtraction algorithm automatically then selects a plurality of points (e.g., pixels) within the first image frame (block 904). In the exemplary case of FIG. 55A, four selected points are highlighted in green. Next, the polarization subtraction algorithm automatically selects homologous points. The homologous points are highlighted in green in the second image frame shown in FIG. 55B.

Once the homologous points are selected, an imaging processing tool invoked by the polarization subtraction algorithm uses pairs of the plurality of points and pairs of the homologous points to calculate a spatial transformation (block 904). For example, this processing step could be performed using the Matlab® function “cp2tform.” After the spatial transformation has been calculated, the polarization subtraction algorithm transforms the second image frame by invoking an imaging processing tool that transforms the second image in accordance with the previously calculated spatial transformation (block 910). In this case, the process of block (910) could be performed using the Matlab® function “imtransform.” FIG. 55C illustrates the resulting transformation of the second image frame.

Next, the polarization subtraction algorithm automatically selects homologous regions of a sclera captured in the transformed first image frame shown in FIG. 55C and the first image frame shown in FIG. 55D (block 912). Once the homologous regions are selected, the polarization subtraction algorithm automatically calculates a ratio of mean intensities in the selected homologous regions between the first image frame and the second image frame is calculated (block 914).

Next, based on the calculated intensity ratio, the intensities in the second image frame are scaled automatically by the polarization subtraction algorithm (block 916). FIG. 55E shows an example of a resulting transformed and intensity scaled second image frame. At this point, the polarizer subtraction algorithm subtracts the transformed and intensity scaled second image frame from the first image frame, which results in a polarization subtraction image such as the polarization subtraction image shown in FIG. 55F.

The importance of the lipid layer on dry eye syndrome has been well studied (See FIG. 1 for the lipid layer on the cornea of the eye). The creation of normal tear film is a continuous process and the etiology has been well described (see LipiView prior art). With adequate meibomian gland function and proper blinking, proper tear film is maintained. One method of visualizing the duration of tear film is to ask a patient to keep their eyes open and visualizing the tear film through the use of fluorescein strips or other devices. In patients with dry eyes, the tear film is less stable, and breaks up faster and results in a quicker break-up time. Longer durations before tear film break-up indicates healthier tear film and meibomian gland function.

One known method for determining tear break-up time is Fluorescein Break-up Time (FBUT). FBUT is performed with a strip of fluorescein that is applied in the lower eyelid fornix and then quickly removed. The patient will be asked to blink three times and then look into the slit lamp without trying to blink. Using a cobalt-blue filtered light and a slitlamp microscope, a measurement is taken of the amount of time that elapses from the last blink and appearance of the first break in the tear film (a break will be seen by the appearance of a dark spot in the blue field). Typically in clinical practice this is done with a stop watch. FBUT of less than 10 seconds or less is consistent with dry eyes.

However, there are problems with FBUT. For example, the physical application of the fluorescein filter paper strip to the conjunctiva can stimulate tearing. In addition, the mere presence of fluorescein may change the properties of the tear film. Other methods have been tried to avoid using fluoresecein, such as using a keratometer, a keratoscope, or a Tearscope. These methods are termed Non Invasive Break-up Time, or NIBUT. Another technique is to analyze the prerupture phase of the tear film break-up referred to as Tear Thinning Time, or TTT, in which the distortion that occurs on the image of the eye is viewed. However, in all of these methods, the improper use of a stop watch can result in error. None of these methods provide a quantitative method of determining an amount of time for an area of interest to change on a surface of an eye.

Further, dry eye sufferers are affected in their abilities to perform everyday activities due to the persistent irritation and eye strain that can occur as a result of long periods of computer terminal use. Deficiency in their lipid layer thickness of the eye can be exasperated by partial or incomplete blinking. For example, the number of complete blinks would increase the higher the position of gaze of the individual. So if an individual were looking at a computer which was ten (10) degrees above eye level, they would need more complete blinks than if the computer were at eye level. Similarly if the computer monitor were placed below eye level significantly, there would be the need for fewer blinks because the rate of evaporation from the eye would decrease as the height of the exposed aperture decreases. These factors have been studied and published as work place safety and ergonomic studies have indicated the effect eye strain on productivity and worker satisfaction. Besides eye level position, other qualifiers are a factor, such as the context of the work, local humidity, type of task, age, skin color etc. of any one individual.

Thus, there is also a need to be able to observe blinking in a standardized method to determine whether or not the lids touched during the blinking process. The importance of the lipid layer on dry eye syndrome has been well studied (See FIG. 1 for the lipid layer on the cornea of the eye). The blink of the upper eyelid can maintain a sufficient lipid layer and the normal blink, defined by complete closure of the upper eyelid to the lower eyelid may not always occur.

In this regard, in another embodiment, the OSI device described herein, or any other suitable imaging device (e.g. any imaging device with image recognition technology), can be used with or without fluorescein strips, in order to determine tear break-up times in an effective manner. The OSI device described herein, or any other suitable imaging device, can be used as described herein, and in combination with fluorescein, to be more effective in determining tear break-up time that with just fluorescein alone. Applying fluorescein to the cornea/lipid layer before imaging will provide different information in the images for processing than if imaging is done without first disposing fluorescein on the cornea.

Accordingly, in one embodiment, the OSI device described herein, or any other suitable imaging device, may be used to analyze images on the cornea of a patient who is instructed to not blink in terms of color pattern, as done in FBUT. The OSI device or imaging device may also analyze the distortion of the tear film image as described by TTT, as well as the change in the lipid layer thickness as described herein. In addition, the OSI device may show by interferometry the presence of a lipid layer or an absence of a lipid layer.

Using videography and an illumination technique that provides diffuse light over the bottom third or half of the eye, the OSI device described herein, or any other suitable imaging device, may be configured to record the amount of time in which an image is provided from the tear film onto the recording apparatus during the non-blinking time of a patient. This would allow a time measurement to be developed for FBUT, NIBUT, or TTT that would be quantitative and provide more clinically relevant information of the condition on the surface of the cornea. Since the OSI device will record the time that the image of interest on the tear film changes as described below, a time measurement can be created for FBUT, NIBUT, or TTT.

In one embodiment, as shown in FIGS. 56A-56D, the aperture of the eye can be divided into a number of different recording segments. For example, FIG. 56A depicts the surface of the eye divided by horizontal lines for observing and recording the area of interest in the tear film. FIGS. 56B, 56C, and 56D illustrate alternate embodiments of segmenting the surface of the eye and capturing images for observing and recording the area of interest in the tear film. In FIG. 56B, the surface of the eye is divided by curvilinear lines for observing and recording the area of interest in the tear film. In FIG. 56C, the surface of the eye is divided by concentric circles for observing and recording the area of interest in the tear film. In FIG. 56D, the surface of the eye is divided into a plurality of pie-shaped segments for observing and recording the area of interest in the tear film. The imaging techniques for doing this have been described previously above and can utilize both polarization and background subtraction techniques. For example, in embodiment, the devices shown in FIG. 6A, FIG. 13, FIG. 14A, FIG. 19A, 21A, 23A, and/or 24A may be used. A patient is placed relative to the imaging apparatus such that an image on the eye can be observed, recorded and analyzed by videography and computer software. To observe and record the area of interest, the time duration for analysis and recording the image on the eye may be longer than what is currently used for imaging. For instance, a patient may be asked to stare at targets or images for a predetermined time period while data collection is being performed.

For example, in one exemplary method, as shown in FIG. 57, a patient and their ocular tear film is adjusted to the imaging device (block 918). A light source, which may be a polarized light source in one embodiment, is positioned relative to the ocular tear film (block 920). The tear film is then illuminated with the light source (block 922). The imaging device is controlled to focus on the interference pattern(s) from specularly reflected light from the ocular tear film (block 924). The imaging device will then capture one or more images of the area of interest of the tear film including the interference pattern(s) from specularly reflected light from the tear film and reduced background signal(s) (block 926).

Over a duration of time while a patient is not blinking, or has not blinked, the surface of the tear film can be analyzed. The area of interest can be:

1. Cobalt blue area field and the appearance of a black spot indicating break-up with FBUT.

2. The distortion of an image caused by the break-up of a lipid layer or thinning of the lipid layer for TTT.

3. The disappearance of a lipid layer during a non-blink as seen with the OSI or other imaging device (this would be seen as a spot where the interferometry would indicate that no lipid is present in a certain location).

Thus, a method and apparatus is disclosed that would utilize the OSI device described herein or any other suitable imaging system for determining the Tear Break-up Time over a given time duration while a patient is not blinking. This information can be utilized to determine the quality of a patient's tear film. The imaging device can record and eliminate “no image” time durations during a patient blink and would also calculate the amount of time elapsed while observing the area of interest. The surface of the eye can be sectioned and segregated for calculation purposes as shown in FIGS. 56A-56D.

In another embodiment, the OSI device described herein can also be used to analyze additional areas of interest and threshold events. For example, referring back to FIG. 25A, the control system and other internal components of the OSI device may be used to capture images of different portions of a patient's tear film and process those images. In addition, the images may be processed in various manners.

The OSI or other imaging device may be operated using a user interface program, which may be provided in a user interface system, such as user interface system 378 (see FIG. 25A) that drives various graphical user interface (GUI) screens on a display of the OSI device or other imaging device. Some examples of control and accesses have been previously described above. Examples of these GUI screens from this GUI are illustrated in FIGS. 44-48 and described above. The GUI screens allow access to the control system 340 in the OSI device 170 and to features provided therein. As illustrated in FIG. 47, a login GUI screen 620 is illustrated. The login GUI screen 620 may be provided in the form of a GUI window 621 that is initiated when a program is executed. The login GUI screen 620 allows a clinician or other user to log into the OSI device 170. Various processing techniques can be implemented using the GUI described above.

For example, in one embodiment, a general process is disclosed for capturing and processing images of an eye to determine tear break-up time, as shown in FIG. 58. An imaging device, such as the OSI device described herein, may be used to image and pre-process an image, as described herein. For example, once the patient has been positioned and an image of a particular portion of the eye is captured, as described in FIG. 57, the image(s) may be pre-processed (block 928). Then, the user waits for no blink of the eye (block 930). The imaging device is focused on an area of interest (block 932). A determination is made as to whether the patient blinks or not (block 934). If the patient blinks, steps 932 and 934 are repeated. If the patient does not blink, a time recording instrument is begun (step 936). The image is then observed to see if there is any change in the area of interest (block 938). This may include processing of the image using any suitable technique, including but not limited to those described herein (block 940). A determination is made as to whether any change in the area of interest of the image has reached a threshold level (block 942). This may include processing of the image using any suitable technique, including but not limited to those described herein (block 943). If the threshold level is not reached, the scan of the area of interest is continued. If the threshold level is reached, then the time of the break-up (as shown by the time recording instrument) is noted (block 944). The break-up time, as well as the image or area of interest, can be displayed to the user via a display of the OSI device or other imaging device (block 946). In one embodiment, the image or area of interest as the threshold level is reached may be displayed. In another embodiment, the image or area of interest before the threshold level is reached is shown together with the image or area of interest after the threshold level is reached.

The general process illustrated in FIG. 58 can be used for specific processing to determine various break-up times. For example, in one embodiment, a tear break-up time may be determined by using a FBUT technique using a cobalt blue field, as shown in FIG. 59. Once the patient has been positioned and an image of a particular portion of the eye is captured, as described in FIG. 57, the image is scanned for blue color hues and consistency (block 948). If the image is inconsistent, wait for the next blink of the eye (block 950). A determination can be made as to whether fluorescein needs to be applied or reapplied (block 952). The imaging device continues to scan and search for a change in the image, such as a black spot image (block 954). Any change in the blue field is noted and a determination is made to see if it is a black spot (block 956). If the black spot doesn't reach a threshold level (block 958), the imaging device continues to scan. When the black spot image appears of a certain size (i.e. it is detectable by a camera), the amount of time from the start of the scan is noted and reported to the user (block 960). Camera images pre and post threshold event can be shown and analyzed (block 962).

In another embodiment, the OSI or other imaging device can be used to determine a Tear Thinning Time (TTT), as shown in FIG. 60. Once the patient has been positioned and an image of a particular portion of the eye is captured, as described in FIG. 57, the image is scanned for interferometry patterns indicating the lipid layer (block 964). The imaging device continues to scan lipid layer patterns (block 966). If the patient blinks (block 967), steps 964 and 966 are repeated. Any change in the pattern of the lipid layer is noted (block 968). If the change in the pattern of the lipid layer does not reach a threshold level, the scan is continued (block 970). When the change in the lipid layer pattern reaches a threshold level, the time is noted (block 972). The break-up time may then be noted to the user (block 974). Camera images pre and post threshold event can be shown and analyzed (block 976).

In another embodiment, the OSI or other imaging device can be used to determine a NIBUT, as shown in FIG. 61. Once the patient has been positioned and an image of a particular portion of the eye is captured, as described in FIG. 57, the image is scanned for interferometry indicating lipid layer thickness across a field of the image (block 978). The imaging device continues to scan the lipid layer and lipid layer thickness is noted (block 980). If the patient blinks (block 981), steps 978 and 980 are repeated. Any change in the lipid layer indicating an absence of lipid is noted (block 982). If the change does not reach a threshold level, the scan is continued (block 984). When the change in lipid thickness reaches a threshold level, the time is noted (block 986). The break-up time may then be noted to the user (block 988). Camera images pre and post threshold event can be shown and analyzed (block 990).

In another embodiment, as shown in FIGS. 62A and 62B, the OSI device or other imaging device may be programmed to look at alternating segments of the cornea surface for the area of interest. In addition, the OSI device or other imaging device may be configured to alternate the light source with a cobalt blue filter or other lighting filter to focus on the area of interest. The imaging device would look at one segment, then another, and then repeat the process until a threshold event occurred or until the patient blinks. If the patient blinks, the process would need to be repeated and the patient would be asked to force the eyes to remain open for this analysis. The segmenting of the cornea surface could be done in multiple ways, including those shown in FIGS. 56A-56D. The segmenting of the corneal surface may include, but is not limited to: by quadrants, by pie shaped segments, by horizontal segments, by vertical segments, and/or by concentric circles.

Referring to FIGS. 62A and 62B, an exemplary process is illustrated where an imaging device, such as the OSI device described herein, may be used to image and pre-process an image, as described herein. For example, once the patient has been positioned and an image of a particular portion of the eye is captured, as described in FIG. 57, the image(s) may be pre-processed (block 992). Then, the user waits for no blink of the eye (block 994). The imaging device is focused on an area of interest (block 996). A determination is made as to whether the patient blinks or not (block 998). If the patient blinks, steps 994 and 996 are repeated. If the patient does not blink, a tiling and scanning sequence is begun (block 1000) and a time recording instrument is begun (block 1002). Certain segments A of the image are analyzed (step 1004). The light source is then alternated with cobalt blue to analyze segments A (step 1006). Certain segments B of the image are analyzed (block 1008). The light source is then alternated with cobalt blue to analyze segments B (step 1010). The steps of alternating between the light source and the cobalt blue filter and analyzing segments A and B is repeated as long as there is no blink (block 1012). If there is a blink (block 1013), the process returns to block 994 and starts over. As long as there is no blink, the segments A and B of the image are observed to see if there is any change in the area of interest (block 1014). This may include processing of the image using any suitable technique, including but not limited to those described herein (block 1016). A determination is made as to whether any change in the area of interest of the image has reached a threshold level (block 1018). This may include processing of the image using any suitable technique, including but not limited to those described herein (block 1020). If the threshold level is not reached, the scan of the area of interest is continued. If the threshold level is reached, then the time of the break-up (as shown by the time recording instrument) is noted (block 1022). The break-up time, as well as the image or area of interest, can be displayed to the user via a display of the OSI device or other imaging device (block 1024). In one embodiment, the image or area of interest as the threshold level is reached may be displayed. In another embodiment, the image or area of interest before the threshold level is reached is shown together with the image or area of interest after the threshold level is reached.

In another embodiment, the OSI device described herein, or any other suitable imaging device, may be used to observe blinking in a standardized method to determine whether or not the lids touched during the blinking process. The importance of the lipid layer on dry eye syndrome has been well studied (See FIG. 1 for the lipid layer on the cornea of the eye). The blink of the upper eyelid can maintain a sufficient lipid layer and the normal blink, defined by complete closure of the upper eyelid to the lower eyelid may not always occur. Referring back to FIGS. 2A and 2B, FIG. 2A shows an open eye and FIG. 2B depicts a blink. For the purposes of this discussion, there are two types of blinks; the complete blink in which the upper eyelid makes contact on the lower eyelid throughout the margin of the eyelid, and the partial blink in which a portion or all of the eyelid margin is not in contact with each other. There needs to be a significant percentage of blinks to be complete to maintain the normal lipid layer of the eye. It would be clinically useful to be able to observe blinking in a standardized method to determine whether or not the lids touched during the blinking process. It is only when lids are shut completely, and then reopened, that oil is released from the meibomian glands. The exact ratio of how many blinks should be complete versus those that are partial blinks (i.e. where the lids do not touch) has never been determined. The study of blink rate is voluminous but there has not been a quantifiable study on the amplitude of the blink, types of blinks (complete versus partial) during a specific time periods, or the percentage of blinks that adequately resurface the cornea with lipids. Determining the amount of travel of the blink will indicate what is normal and not normal for these patients. With this information, the clinician can better inform patients, provide exercises, or propose additional therapy to alleviate the symptoms of dry eye. The OSI device described herein, or any other suitable imaging device, may be used to observe blinking in a standardized method to determine whether or not the lids touched during the blinking process, as described more fully below.

The method and apparatus described herein may include the OSI device described herein, or any other suitable imaging device, configured to calculate the amplitude of blinks and determine whether eye lid margin contact was complete over a given time duration. This information can be tied with the productivity of each blink in terms of enriching the lipid layer thickness. Lid margin contact can be expressed as a percentage of travel, for instance full contact could be considered 100% travel. As an example, an upper eye lid travel that only reached the bottom of the pupil would be considered 60% travel. The OSI or other imaging device would record “no image” time durations during a complete blink and would also calculate the percentage of surface area during partial imaging segments.

FIG. 63A illustrates a complete blink and FIG. 63B shows an increased aperture due to an upper gaze by the patient. FIG. 63C shows key landmarks in the upcoming discussion: 1026—upper eyelid, 1028—distance to the center of the pupil, and 1030—amplitude of upper eyelid travel.

Using videography and an illumination technique that provides diffuse light over the bottom third of the eye, an imaging device, such as the OSI device described herein in one embodiment, is used to record the amount of time in which no image is provided from the tear film onto the recording apparatus. This would allow an index to be developed that would be quantitative and provide more clinically relevant information of how the upper eyelid came over the pupil. Since the OSI or other imaging device, or any other instrument, will record the time that there is no image from the tear film, a metric can be developed which totals the frequency and also amount of time of zero or partial image. The aperture of the eye can be divided into a number of different recording segments. For example, as previously discussed, the surface of the eye can be sectioned and segregated for calculation purposes as shown above in FIGS. 56A-56D. FIG. 56A depicts the surface of the eye divided by horizontal lines for observing and recording the amplitude of travel of the upper eyelid. FIGS. 56B-56D illustrate alternate embodiments of segmenting the surface of the eye and image for observing and recording the amplitude of upper eyelid travel.

Over a predetermined time duration, the number of complete and partial blinks can be recorded, studied, and analyzed as it pertains to complete, partial, or non-productive blinks. For example, FIG. 6A, FIG. 13, FIG. 14A, FIG. 19A, 21A, 23A, and/or 24A illustrate a patient within an imaging apparatus in which the image on the eye can be observed, recorded and analyzed by videography and computer software. To observe and record these ratios, the time duration for analysis and recording the image on the eye may be long. For instance, a patient may be asked to stare at targets or images for a predetermined time period while data collection is being performed.

As an example of determining the amplitude of upper eyelid travel, in the eye open condition, the position of the upper eyelid can be determined and normalized by the center of the pupil position. As the upper eyelid travels downward, the surface area of available image will decrease and can be recorded and analyzed. When no image is available to the imaging device, the blink is considered complete and if a partial image is available along the margin of the eyelid, the blink is categorized as partial. In addition, the resulting thickness of lipid layer on the return travel of the upper eyelid can provide an indication of the productivity of the travel of the upper eyelid.

An example of this is found in FIG. 10, which shows a normal eye image, and FIG. 11, which illustrates an image using interferometry for studying lipid layer thickness.

The parameters that could be studied using the apparatuses and methods disclosed herein include:

1. Frequency of complete blinks versus partial blinks expressed as a ratio.

2. Number of complete blinks within a time duration.

3. Amplitude of the blink or travel of the upper eyelid.

4. The number of incomplete blinks recorded and the percentage of the exposed aperture of the eye. Not all incomplete blinks are the same. Some incomplete blinks are more like an eyelid flutter and others are almost complete blinks. The degree of incompleteness of eyelid blinks can be categorized and set to an appropriate level of therapy.

5. The mean amount of exposed aperture during incomplete blinking expressed as a percentage of surface area.

6. The productivity of the blinks as determined by the thickness of the resulting lipid layer on the eye after the blink.

7. The percentage of productive blinks within a given time duration.

8. Other parameters such as the speed of the upper eyelid travel and time duration in the closed position can be determined depending upon the sample rate of the recording mechanism.

The apparatuses and methods disclosed herein could aid in quantifying these parameters for a given patient. Understanding these values could be of significant clinical importance for a patient suffering from dry eye.

Many modifications and other embodiments of the present disclosure set forth herein will come to mind to one skilled in the art to which the disclosure pertains having the benefit of the teachings presented in the foregoing descriptions and the associated drawings. These modifications include, but are not limited to, the type of light source or illuminator, the number of polarizers, the type of imaging device, image device settings, the relationship between the illuminator and an imaging device, the control system, the type of tear film interference model, and the type of electronics or software employed therein, the display, the data storage associated with the OSI device for storing information, which may also be stored separately in a local or remotely located remote server or database from the OSI device, any input or output devices, settings, including pre-processing and post-processing settings. Note that subtracting the second image from the first image as disclosed herein includes combining the first and second images, wherein like signals present in the first and second images are cancelled when combined. Further, the present disclosure is not limited to illumination of any particular area on the patient's tear film or use of any particular color value representation scheme. Also, the present disclosure is not limited to imaging devices that incorporate interferometry. Standard imaging techniques with image recognition technology would be sufficient for picking up color patterns or other item of interest.

Alternative embodiments can include different devices for observing and recording blinking. As an example, it may be useful to study a patient within the environment they suffer from the consequences of dry eye as opposed to coming into the physician's office. For instance, a patient can be asked to wear a wire frame that is goggle-sized but does not have lenses. The wire frame would contain a camera to focus on the eye image and record the patient at their work place environment. The absence of the lenses would allow for normal environmental factors (humidity, temperature, pollutants, etc.) to normally affect the eye. Images would be recorded over predetermined time durations and can be downloadable to the physician for analysis. The analysis would include information on the number of blinks, frequency of partial blinks, the productivity of blinking in terms of lipid layer thickness, and/or the parameters mentioned earlier.

Therefore, it is to be understood that the present disclosure is not to be limited to the specific embodiments disclosed and that modifications and other embodiments are intended to be included within the scope of the appended claims. It is intended that the present disclosure cover the modifications and variations of this disclosure provided they come within the scope of the appended claims and their equivalents. Although specific terms are employed herein, they are used in a generic and descriptive sense only and not for purposes of limitation. 

What is claimed is:
 1. An apparatus for determining a break-up time of an ocular tear film, comprising: a control system configured to: (a) receive at least one first image of an area of interest of an ocular tear film captured by an imaging device while illuminated by a light source; (b) start a time measurement instrument; (c) receive at least one second image of the area of interest of the ocular tear film captured by the imaging device while illuminated by the light source; (d) analyze the at least one first image and the at least one second image to determine if a change has occurred in the area of interest; (e) if a change has occurred in the area of interest, determine if a threshold level has been reached; and (f) if the threshold level has been reached, measure an amount of time from the start of the time measurement instrument until a time that the threshold level has been reached.
 2. The apparatus of claim 1, wherein the control system is further configured to display the amount of time from the start of the time measurement instrument until a time that the threshold level has been reached on a visual display associated with a user.
 3. The apparatus of claim 1, wherein the control system is further configured to display, on a visual display associated with a user, an image of the area of interest of the ocular tear film before the time the threshold level was reached and to display an image of the area of interest of the ocular tear film after the time the threshold level was reached.
 4. The apparatus of claim 1, further comprising an imaging device configured to capture the at least one first image and capture the at least one second image.
 5. The apparatus of claim 4, wherein the imaging device is configured to capture an area of interest, wherein the area of interest is divided into a plurality of different segments.
 6. The apparatus of claim 5, wherein the area of interest is divided into a plurality of different horizontal segments by one or more horizontal lines.
 7. The apparatus of claim 5, wherein the area of interest is divided into a plurality of different segments by one or more curvilinear lines.
 8. The apparatus of claim 5, wherein the area of interest is divided into a plurality of concentric circular segments by one or more concentric circles.
 9. The apparatus of claim 5, wherein the area of interest is divided into a plurality of different pie-shaped segments.
 10. The apparatus of claim 1, wherein the imaging device is configured to capture an image of an area of interest of the ocular tear film that includes at least one interference pattern from specularly reflected light from the ocular tear film and reduced background signals.
 11. The apparatus of claim 1, wherein the area of interest is a cobalt blue area field and the change in the area of interest is an appearance of a black spot indicating tear break-up caused by fluorescein.
 12. The apparatus of claim 1, wherein the change in the area of interest is a change in a pattern of the lipid layer of the ocular tear film.
 13. The apparatus of claim 1, wherein the change in the area of interest is a change in a thickness of the lipid layer of the ocular tear film.
 14. The apparatus of claim 13, wherein the change in the thickness of the lipid layer of the ocular tear film is indicative of an absence of liquid in the lipid layer.
 15. An apparatus for determining a break-up time of an ocular tear film, comprising: a control system configured to: (a) receive at least one first image of an area of interest of an ocular tear film captured by an imaging device while illuminated by a light source of a first type, wherein the area of interest is divided into a plurality of segments and the at least one first image is of a first segment of the plurality of segments; (b) start a time measurement instrument; (c) receive at least one second image of an area of interest of an ocular tear film captured by an imaging device while illuminated by a light source of the first type, wherein the area of interest is divided into a plurality of segments and the at least one second image is of the first segment of the plurality of segments; (d) analyze the at least one first image and the at least one second image to determine if a change has occurred in the area of interest; (e) receive at least one third image of an area of interest of the ocular tear film captured by the imaging device while illuminated by a light source of a second type, wherein the area of interest is divided into a plurality of segments and the at least one third image is of a second segment of the plurality of segments; (f) receive at least one fourth image of an area of interest of the ocular tear film captured by the imaging device while illuminated by a light source of a second type, wherein the area of interest is divided into a plurality of segments and the at least one fourth image is of the second segment of the plurality of segments; (g) analyze the at least one third image and the at least one fourth image to determine if a change has occurred in the area of interest; (h) if a change has occurred in the area of interest based on one or more of the at least one first image, at least one second image, at least one third image, and at least one fourth image, determine if a threshold level has been reached; and (i) if the threshold level has been reached, measure an amount of time from the start of the time measurement instrument until a time that the threshold level has been reached.
 16. The apparatus of claim 15, wherein the light source of the first type is a polarized light source.
 17. The apparatus of claim 15, wherein the light source of the second type is a light source with a cobalt blue filter.
 18. A method for determining a break-up time of an ocular tear film, comprising: (a) receiving at least one first image of an area of interest of an ocular tear film captured by an imaging device while illuminated by a light source; (b) starting a time measurement instrument; (c) receiving at least one second image of the area of interest of the ocular tear film captured by the imaging device while illuminated by the light source; (d) analyzing the at least one first image and the at least one second image to determine if a change has occurred in the area of interest; (e) if a change has occurred in the area of interest, determining if a threshold level has been reached; and (f) if the threshold level has been reached, measuring an amount of time from the start of the time measurement instrument until a time that the threshold level has been reached.
 19. The method of claim 18, further comprising displaying the amount of time from the start of the time measurement instrument until a time that the threshold level has been reached on a visual display associated with a user.
 20. The method of claim 18, further comprising displaying, on a visual display associated with a user, an image of the area of interest of the ocular tear film before the time the threshold level was reached and to display an image of the area of interest of the ocular tear film after the time the threshold level was reached.
 21. A method for determining a break-up time of an ocular tear film, comprising: (a) receiving at least one first image of an area of interest of an ocular tear film captured by an imaging device while illuminated by a light source of a first type, wherein the area of interest is divided into a plurality of segments and the at least one first image is of a first segment of the plurality of segments; (b) starting a time measurement instrument; (c) receiving at least one second image of an area of interest of an ocular tear film captured by an imaging device while illuminated by a light source of the first type, wherein the area of interest is divided into a plurality of segments and the at least one second image is of the first segment of the plurality of segments; (d) analyzing the at least one first image and the at least one second image to determine if a change has occurred in the area of interest; (e) receiving at least one third image of an area of interest of the ocular tear film captured by the imaging device while illuminated by a light source of a second type, wherein the area of interest is divided into a plurality of segments and the at least one third image is of a second segment of the plurality of segments; (f) receiving at least one fourth image of an area of interest of the ocular tear film captured by the imaging device while illuminated by a light source of a second type, wherein the area of interest is divided into a plurality of segments and the at least one fourth image is of the second segment of the plurality of segments; (g) analyzing the at least one third image and the at least one fourth image to determine if a change has occurred in the area of interest; (h) if a change has occurred in the area of interest based on one or more of the at least one first image, at least one second image, at least one third image, and at least one fourth images, determining if a threshold level has been reached; and (i) if the threshold level has been reached, measuring an amount of time from the start of the time measurement instrument until a time that the threshold level has been reached.
 22. An apparatus for determining lid margin contact and/or blink rate of an eye having an upper eyelid and a lower eyelid, comprising: a control system configured to: (a) receive at least one image of an area of interest of an eye captured by an imaging device when illuminated by a light source, wherein the at least one image is captured by the imaging device over a given period of time; (b) analyze the at least one image to determine a number of complete blinks of the eye for the given period of time.
 23. The apparatus of claim 22, wherein the control system is further configured to analyze the at least one image to determine a number of partial blinks of the eye for the given period of time.
 24. The apparatus of claim 22, wherein the control system is further configured to calculate the number of complete blinks by analyzing the at least one image to determine whether or not the upper eyelid and the lower eyelid touched during a blink that occurred during the given time period, and if the upper eyelid and the lower eyelid touched during the blink, counting it as a complete blink.
 25. The apparatus of claim 23, wherein the control system is further configured to analyze the at least one image and calculate an amplitude of one or more of the partial blinks.
 26. The apparatus of claim 25, wherein the control system is configured to calculate the amplitude of one or more of the partial blinks based on an amount of travel of the upper eyelid.
 27. The apparatus of claim 26, wherein the amount of travel of the upper eyelid is measured by comparing how far the upper eyelid travels in relation to a pupil of the eye.
 28. The apparatus of claim 22, wherein the image of the area of interest of the eye comprises an ocular tear film, and a complete blink of the eye is counted if the upper eyelid travels downward toward the lower eyelid to an extent that no image is provided from the ocular tear film.
 29. The apparatus of claim 22, wherein the area of interest of the eye comprises an ocular tear film, and a partial blink of the eye is counted if the upper eyelid travels downward toward the lower eyelid and a partial image of the eye is still visible from the image provided from the ocular tear film.
 30. The apparatus of claim 22, wherein the control system is further configured to analyze the at least one image of the area of interest of the eye and determine a number of complete blinks and a number of partial blinks for the given period of time based on an amount of travel of the upper eyelid as measured by how far the upper eyelid travels in relation to the area of interest.
 31. The apparatus of claim 23, wherein the control system is further configured to calculate a ratio of complete blinks versus partial blinks.
 32. The apparatus of claim 23, wherein the control system is further configured to analyze the at least one image of the area of interest of the eye and determine a degree of completeness for at least one of the partial blinks for the given period of time based on a percentage of an exposed aperture of the eye in the at least one image of the area of interest of the eye.
 33. The apparatus of claim 32, wherein the control system is further configured to analyze the at least one image of the area of interest of the eye and determine a mean amount of exposed aperture of the eye expressed as a percentage of surface areas visible in the at least one image of the area of interest of the eye.
 34. The apparatus of claim 23, wherein the image of the area of interest of the eye comprises an ocular tear film and wherein the control system is further configured to determine a productivity of one or more of the blinks based on a thickness of a lipid layer on the eye after the one or more of the blinks.
 35. The apparatus of claim 34, wherein the control system is further configured to calculate a percentage of productive blinks within the given time period.
 36. The apparatus of claim 23, wherein the control system is further configured to determine a speed at which the upper eyelid travels based on an analysis of the at least one image.
 37. The apparatus of claim 23, wherein the control system is further configured to determine an amount of time the eye is in a closed position based on an analysis of the at least one image.
 38. A method for determining lid margin contact and/or blink rate of an eye having an upper eyelid and a lower eyelid, comprising: (a) receiving at least one image of an area of interest of an eye captured by an imaging device when illuminated by a light source, wherein the at least one image is captured by the imaging device over a given period of time; (b) analyzing the at least one image to determine a number of complete blinks of the eye for the given period of time. 